JP2012035056A - Breathing level measuring device and breathing level measuring system - Google Patents

Abstract

A device capable of accurately and easily measuring the ventilation capacity of each of the right lung and left lung of a subject is provided.
A biometric apparatus includes a bioelectrical impedance measuring unit that measures bioelectrical impedance of a specific part of the body, and a CPU. The CPU 170 controls the bioelectrical impedance measuring unit 200 so as to measure the bioelectrical impedance of the part including the right lung of the subject and the bioelectrical impedance of the part including the left lung. Then, the CPU 170 obtains the right lung respiration level indicating the ventilation capacity of the right lung based on the measured value of the bioelectrical impedance of the part including the right lung, while based on the measured value of the bioelectrical impedance of the part including the left lung. The left lung respiration level indicating the ventilation capacity of the left lung is obtained.
[Selection] Figure 1

Description

  The present invention relates to an apparatus and system for measuring a respiratory level indicative of a subject's lung ventilation capability.

  Various devices that measure bioelectric impedance and estimate the state of a living body based on the measurement result have been known. As one of such devices, Patent Document 1 discloses a technique for estimating vital capacity based on trunk bioelectrical impedance.

Japanese Patent Laying-Open No. 2007-50127 (see paragraph 0020)

By the way, there are two human lungs on the left and right. When healthy, there is no functional difference (difference in ventilation capacity) between the right lung (referred to as the right lung) and the left lung (left lung), but there is a disease in either the left or right lung When there is a difference, a functional difference is generated between the right lung and the left lung. However, it has been difficult to accurately and easily measure the ventilation capacity of each of the right lung and the left lung with the conventional technology.
Therefore, an object of the present invention is to provide an apparatus and system that can accurately and easily measure the ventilation capacity of each of the right lung and left lung of a subject.

  In order to solve the above-described problem, a respiration level measurement apparatus (1) according to the present invention includes a bioelectrical impedance measuring unit (170) that measures bioelectrical impedance for a part including a right lung and a part including a left lung of a subject. 200), and the right lung respiration level indicating the ventilation capacity of the right lung is obtained based on the measurement value of the bioelectrical impedance of the part including the right lung, while the measurement value of the bioelectrical impedance of the part including the left lung is obtained. And a respiration level calculation unit (170) for obtaining a left lung respiration level indicating the ventilation capacity of the left lung. In the present invention, the respiration level calculation unit obtains the right lung respiration level indicating the ventilation capacity of the right lung based on the measurement value of the bioelectric impedance of the region including the right lung, while the bioelectric impedance of the region including the left lung By obtaining the left lung respiration level indicating the ventilation capacity of the left lung based on the measured values of the above, the ventilation capacity of each of the subject's right lung and left lung can be accurately and easily measured.

  As an aspect of the respiratory level measurement device (1) according to the present invention, the bioelectrical impedance measuring unit includes the first bioelectrical impedance on the right side of the upper trunk, including the upper part of the subject's right lung and not including the abdomen, and the left of the subject. The second bioelectrical impedance of the upper left side of the trunk including the upper part of the lung and not including the abdomen is measured, and the respiration level calculating unit determines the ventilation capacity of the upper part of the right lung based on the measured value of the first bioelectrical impedance. The first right lung respiration level indicating the ventilation capacity of the upper part of the left lung is obtained based on the measured value of the second bioelectrical impedance.

  When the subject performs breathing consisting of inspiration and expiration, each of the first bioelectrical impedance on the right side of the upper trunk and the second bioelectrical impedance on the left side of the upper trunk changes according to the breathing. Inhalation increases the amount of air contained in the lung tissue, so the bioelectrical impedance of the lung changes in the increasing direction. In expiration, the amount of air contained in the lung tissue decreases, so the bioelectrical impedance of the lung changes in the decreasing direction. . That is, the first bioelectrical impedance on the right side of the upper trunk that includes the upper part of the right lung and does not include the abdomen, and the second bioelectrical impedance on the left side of the upper trunk that includes the upper part of the left lung and does not include the abdomen While changing in the increasing direction, exhalation changes in the decreasing direction. Here, the greater the amount of air entering and exiting the right lung, that is, the greater the amount of ventilation in the right lung, the greater the amplitude value of the first bioelectrical impedance. In the above-described aspect, focusing on the fact that the amplitude value of the first bioelectrical impedance is a value corresponding to the ventilation capacity of the upper part of the right lung, ventilation of the upper part of the right lung based on the measured value of the first bioelectrical impedance. A first right lung respiratory level indicative of ability is determined. On the other hand, the larger the amount of air entering and leaving the left lung, that is, the amount of ventilation of the left lung, the larger the amplitude value of the second bioelectrical impedance. In the above-described aspect, focusing on the fact that the amplitude value of the second bioelectrical impedance is a value corresponding to the ventilation capacity of the upper part of the left lung, ventilation of the upper part of the left lung based on the measured value of the second bioelectrical impedance. A first left lung respiratory level indicative of ability is determined. Thereby, the ventilation capacity of the upper part of the right lung and the ventilation capacity of the upper part of the left lung can be accurately and easily measured.

  For example, in order to measure the bioelectrical impedance of a part including the right lung, it is conceivable to attach a current electrode or a voltage electrode to the right lung portion of the surface of the trunk of the subject. Moreover, in order to measure the bioelectrical impedance of the region including the left lung, it is conceivable to attach a current electrode or a voltage electrode to the left lung portion of the trunk surface of the subject. However, such a method requires time and effort to attach the current electrode and the voltage electrode to the subject. If the limb-guided eight-electrode method is used, current electrodes and voltage electrodes are placed on both palms and soles so that the first bioelectricity on the right side of the upper trunk, including the upper part of the subject's right lung and not including the abdomen. Impedance and the second bioelectric impedance on the left side of the upper trunk, which includes the upper part of the subject's left lung and does not include the abdomen, can be measured. For this reason, it is not necessary to affix a current electrode or a voltage electrode on a test subject's trunk.

  As an aspect of the respiratory level measurement apparatus (1) according to the present invention, a first centering value indicating the amplitude reference level of the measurement value of the first bioelectrical impedance and an amplitude reference level of the measurement value of the second bioelectrical impedance are shown. A first centering value generation unit (170) that generates a second centering value, and a first relative value calculation unit (170) that calculates a first relative value that is a relative value of the measurement value of the first bioelectrical impedance to the first centering value. ) And a second relative value calculation unit (170) that obtains a second relative value that is a relative value of the measurement value of the second bioelectrical impedance to the second centering value, and the respiration level calculation unit includes the first Preferably, the first right lung respiratory level is determined based on the relative value, while the first left lung respiratory level is determined based on the second relative value. A 1st centering value is an amplitude reference level for extracting the information resulting from respiration from the waveform which shows the time-dependent change of the 1st bioelectrical impedance accompanying respiration. The second centering value is an amplitude reference level for extracting information resulting from respiration from a waveform indicating a change with time of the second bioelectric impedance accompanying respiration.

  In the above-described aspect, the respiratory level calculation unit obtains the first right lung respiratory level and the first left lung respiratory level based on the first relative value and the second relative value indicating information resulting from the breathing. The ventilation capacity of the upper part of the right lung and the ventilation capacity of the upper part of the left lung can be measured more accurately. The respiration level calculation unit calculates, for each respiration of the subject, the sum of absolute values of the maximum value and the minimum value of the first relative value in the one respiration as the first right lung respiration level, For example, the sum of absolute values of the maximum value and the minimum value of the second relative value in one breath is calculated as the first left lung respiration level.

  The bioelectrical impedance measuring unit measures the first bioelectrical impedance and the second bioelectrical impedance every time the sampling timing is reached at a predetermined cycle. And even if the waveform which shows each change of 1st bioelectrical impedance and 2nd bioelectrical impedance is disturb | confused by the influence by body movement etc., the 1st centering value production | generation part produces the 1st centering value and 2nd according to it. A first centering value is generated based on the measured value of the first bioelectrical impedance at each of a predetermined number of sampling timings so that the centering value is obtained, and based on the measured value of the second bioelectrical impedance at each sampling timing. To generate a second centering value. More specifically, for each sampling timing, the first centering value generator generates a plurality of samplings within a centering period starting from a time point a predetermined time length before the sampling timing and ending with the sampling timing. The moving average process is performed using the measurement value of the first bioelectrical impedance at each timing, and based on the result, the first centering value at the sampling timing is generated, while the second bioelectrical impedance at each sampling timing is generated. A moving average process is performed using the measured value, and a second centering value at the sampling timing is generated based on the result. As a result, even if the waveforms indicating changes in the first bioelectric impedance and the second bioelectric impedance are disturbed due to the influence of body movement or the like, the first centering value and the second centering value corresponding thereto can be generated with high accuracy. Moreover, it is preferable that the time length of the centering period is variably set according to the breathing rate of the subject. The “moving average process” includes not only an unweighted average process but also an average process with a weight. For example, an aspect in which averaging processing is performed after weighting according to a difference in frequency at each sampling timing may be employed.

  In the above-described aspect, not only the first right lung respiratory level and the first left lung respiratory level, but also the second right lung respiratory level indicating the ventilation ability of the middle lower part of the right lung, A second left lung respiratory level indicative of ventilation capability can also be measured. When the subject breathes, the bioelectrical impedance of the middle trunk changes according to the breathing, and the third living body on the right side of the middle trunk including the middle lower part of the right lung and the abdomen increases as the amount of ventilation in the right lung increases. While the amplitude value of the electrical impedance increases, the amplitude value of the fourth bioelectrical impedance on the left side of the middle trunk including the middle lower part and the abdomen including the left lung increases as the ventilation volume of the left lung increases. In the present invention, focusing on this point, the second right lung respiration level indicating the ventilation capability of the middle lower part of the right lung is obtained based on the measured value of the third bioelectrical impedance, and the measured value of the fourth bioelectrical impedance. The second left lung respiration level indicating the ventilation capability of the middle lower part of the left lung is obtained based on the above. More specifically, every time the bioelectrical impedance measurement unit reaches the sampling timing, the bioelectrical impedance measurement unit and the third bioelectrical impedance on the right side of the middle trunk including the middle lower part and the abdomen of the subject's right lung and the middle part of the subject's left lung The fourth bioelectrical impedance of the upper left side of the trunk including the lower part and the abdomen, the third centering value indicating the amplitude reference level of the measured value of the third bioelectrical impedance, and the measured value of the fourth bioelectrical impedance A second centering value generation unit (170) that generates a fourth centering value indicating the amplitude reference level, and a third relative value for determining a third relative value that is a relative value of the measured value of the third bioelectrical impedance with respect to the third centering value. A value calculation unit (170) and a fourth relative value that is a relative value of the measured value of the fourth bioelectrical impedance to the fourth centering value. A fourth relative value calculation unit (170) for calculating the first bioelectrical impedance, the first zero cross timing at which the first bioelectrical impedance measurement value and the first centering value are equal, and the second bioelectrical impedance measurement value and the second centering value And a zero-cross timing extraction unit (170) that extracts a second zero-crossing timing that is equal to each other, and the second centering value generation unit generates a third based on a measurement value of the third bioelectrical impedance at the first zero-crossing timing. While generating the centering value, the fourth centering value is generated based on the measurement value of the fourth bioelectrical impedance at the second zero-cross timing, and the respiration level calculation unit calculates the middle lower part of the right lung based on the third relative value. While determining the second right lung breathing level indicating the ventilation capacity of the second, based on the fourth relative value, And so that obtaining the second left lung respiration level indicating the lower ventilation capacity in the lungs.

  Here, in abdominal breathing, the visceral tissue rises in the direction of pushing up the diaphragm by the action of the abdominal skeletal muscle during expiration, so the bioelectrical impedance of the abdomen changes in the increasing direction. That is, in the expiration of abdominal breathing, the increase in the bioelectrical impedance of the abdomen cancels the decrease in the bioelectrical impedance of the lungs. On the other hand, this is not the case with chest breathing. Therefore, when the subject's breathing is abdominal breathing, the change in the third bioelectric impedance including the middle lower part and the abdomen of the right lung shows a mode (non-sinusoidal) different from the change in the first bioelectrical impedance described above. . Therefore, as in the case of obtaining the first centering value and the second centering value, even if the moving average process using the measured value of the third bioelectrical impedance at each of the predetermined number of sampling timings is performed, these amplitude references It is difficult to accurately obtain an amplitude reference level (third centering value) for extracting information resulting from respiration from a level, that is, from a waveform indicating a temporal change in the third bioelectric impedance associated with respiration. The same applies to the fourth centering value.

  In the above aspect, the second centering value generation unit generates the third centering value based on the measurement value of the third bioelectrical impedance at the first zero cross timing extracted by the zero cross timing extraction unit, while the zero cross timing extraction A fourth centering value is generated based on the measured value of the fourth bioelectrical impedance at the second zero cross timing extracted by the unit. More specifically, the second centering value generation unit determines whether or not the sampling timing is the first zero cross timing at each sampling timing, and if the sampling timing is the first zero cross timing, Based on the measurement value of the third bioelectrical impedance at the sampling timing, the third centering value at the sampling timing is generated. On the other hand, when the sampling timing is not the first zero cross timing, the third centering value is generated at the sampling timing immediately before the sampling timing. The obtained third centering value is employed as the third centering value at the sampling timing. As a result, even if the subject's breathing is abdominal breathing, the amplitude reference level (third centering value) for extracting information resulting from breathing from the waveform indicating the temporal change in the third bioelectrical impedance is accurately obtained. Can be sought.

  In addition, the second centering value generation unit determines, for each sampling timing, whether or not the sampling timing is the second zero cross timing, and when the sampling timing is the second zero cross timing, 4th centering value in the said sampling timing is produced | generated based on the measured value of 4 bioelectrical impedance, On the other hand, when the said sampling timing is not 2nd zero cross timing, the 4th centering produced | generated at the sampling timing immediately before the said sampling timing The value is adopted as the fourth centering value at the sampling timing. As a result, even if the subject's breathing is abdominal breathing, the amplitude reference level (fourth centering value) for extracting information resulting from breathing from the waveform indicating the temporal change of the fourth bioelectrical impedance is accurately determined. Can be sought. Then, for each breath of the subject, the breathing level calculation unit calculates the sum of absolute values of the maximum value and the minimum value of the third relative value in the breathing as the second right lung breathing level, For example, the sum of the absolute values of the maximum value and the minimum value of the fourth relative value in one breath is calculated as the second left lung respiratory level.

  In addition, the respiratory level measurement apparatus (1) according to the present invention does not measure the first right lung respiratory level and the first left lung respiratory level, and the second right indicating the ventilation ability of the middle lower part of the right lung. It is also possible to measure the pulmonary respiratory level and a second left pulmonary respiratory level indicative of the ventilation capability of the middle lower part of the left lung. In this aspect, the bioelectrical impedance measuring unit includes the third bioelectrical impedance on the right side of the middle trunk including the middle lower part and the abdomen of the subject's right lung and the left side of the middle trunk including the middle lower part and the abdomen of the subject's left lung. The fourth bioelectric impedance is measured, and the respiration level calculation unit obtains the second right lung respiration level indicating the ventilation capability of the middle lower part of the right lung based on the measurement value of the third bioelectric impedance, 4 Based on the measured value of the bioelectrical impedance, the second left lung respiration level indicating the ventilation ability of the middle lower part of the left lung is obtained. In this case as well, the third bioelectric impedance on the right side of the trunk and the left side of the middle part of the trunk can be obtained by arranging the current electrodes and voltage electrodes on both palms and the soles using the limb induction eight electrode method. Since the fourth bioelectrical impedance can be measured, there is no need to attach a current electrode or a voltage electrode to the trunk of the subject.

Moreover, as an aspect of the respiratory level measurement apparatus (1) according to the present invention, the bioelectrical impedance measurement unit (170, 200) includes the upper part of the right lung of the subject and the first bioelectricity on the right side of the upper trunk without including the abdomen. Impedance (ZaR), second bioelectrical impedance (ZaL) on the upper left side of the trunk that includes the upper part of the subject's left lung and does not include the abdomen, and 3 bioelectrical impedance (ZbR) and 4th bioelectrical impedance (ZbL) on the left side of the trunk including the middle lower part and abdomen of the subject's left lung are measured, and the respiration level calculating unit (170) Based on the measurement value of the electrical impedance and the measurement value of the third bioelectrical impedance, the right lung respiration level indicating the ventilation ability of the right lung is obtained, while the measurement value of the second bioelectrical impedance is obtained. Preliminary based on the measured value of the fourth bioelectrical impedance may be obtained left lung respiration level indicating the left lung ventilation capacity.
That is, as the right lung respiratory level indicating the right lung ventilation capacity, both the first right lung respiratory level and the second right lung respiratory level described above are obtained, while the left lung respiratory level indicating the left lung ventilation capacity is obtained. Both the first left lung respiratory level and the second left lung respiratory level described above may be obtained.

  In this case, of the two axes orthogonal to each other, one axis is the first bioelectrical impedance (ZaR) and the other axis is the third bioelectrical impedance (ZbR). The display data of the first Lissajous figure (FIG. 45: for right lung) showing the change over time of the measured value of the electrical impedance is generated, one axis is the second bioelectric impedance (ZaL), and the other axis is the fourth. Display for generating display data of the second Lissajous figure (FIG. 45: for the left lung) indicating the change over time of the measured value of the second bioelectrical impedance and the measured value of the fourth bioelectrical impedance as the bioelectrical impedance (ZbL) A data generation unit (170) may be further provided.

  Note that the two axes orthogonal to each other are, for example, the X axis and the Y axis. However, the present invention is not limited to this. For example, the X axis and the Y axis may be two axes inclined by 45 degrees. In addition, the Lissajous figure may indicate, for example, one breathing state as shown in FIGS. 37 and 38, or a plurality of breathing states continuously as shown in FIGS. 39 and 40. May be shown. The respiration level measuring device may include a display unit that displays the first Lissajous figure and the second Lissajous figure, and the display data of the first Lissajous figure and the display data of the second Lissajous figure are displayed on an external display device. An output unit for outputting to may be provided.

  For example, in the case of thoracic breathing, as shown in FIG. 10, the bioelectrical impedance Za at the upper trunk and the bioelectrical impedance Zb at the middle trunk change in an increasing direction during inspiration, and the bioelectricity at the upper trunk in exhalation. Both the impedance Za and the bioelectric impedance Zb in the middle of the trunk change in a decreasing direction. Therefore, when the proportion of chest breathing in the subject's breathing is extremely high, for example, as shown in FIGS. 37 and 39, right and left lung Lissajous figures (first Lissajous figure and second Lissajous figure) The trajectory is an inclined straight line. Also, if the chest breathing is shallow, the locus of the Lissajous figure becomes small, and if the chest breathing is deep, the locus of the Lissajous figure becomes large.

  On the other hand, in the case of abdominal breathing, as shown in FIG. 9, the bioelectrical impedance Za of the upper trunk and the bioelectrical impedance Zb of the middle trunk change in an increasing direction during inspiration, and the upper trunk of the trunk during exhalation. The bioelectric impedance Za changes in the decreasing direction, while the bioelectric impedance Zb in the middle of the trunk changes in the increasing direction. Therefore, when the subject's breathing includes abdominal breathing, for example, as shown in FIGS. 38 and 40, the locus of the Lissajous figure for the right lung or the left lung has a bent shape.

  Note that the Lissajous figure shown in FIG. 38 is a case where the ratio of the chest breathing and the abdominal breathing to one breath is 50%. In this case, the locus of the Lissajous figure has a boomerang shape ("<" shape), and the shape of the locus is almost symmetrical vertically. However, if the proportion of the abdominal breathing is lower than that of the chest breathing, the locus of the Lissajous figure has a larger proportion of the straight line portion corresponding to the trajectory in the case of the chest breathing (the straight line portion rising to the right in FIG. 38). Thus, the proportion of the bent portion (the straight downward portion in FIG. 38) is reduced. On the contrary, if the proportion of the abdominal breathing is higher than that of the chest breathing, the locus of the Lissajous figure is the proportion of the straight line portion corresponding to the trajectory in the case of the chest breathing (the straight line portion rising to the right in FIG. 38). It becomes smaller, and the proportion of the bent portion (the straight downward portion in FIG. 38) increases. In this way, when the subject's breathing includes abdominal breathing, the trajectory of the Lissajous figure varies in bending shape depending on the ratio of chest breathing and abdominal breathing.

  Theoretically, when the rate of abdominal breathing is 100%, the locus of the Lissajous figure is a straight line inclined in the opposite direction to the locus of chest breathing. However, for example, even when the abdomen is recessed or inflated with the breath stopped and no chest breathing performed, the lungs contract and expand with the diaphragm above and below, Except when the diaphragm does not function at all due to disease or the like, chest breathing is always included when the subject breathes. Therefore, in fact, no matter how high the abdominal breathing rate is, the Lissajous figure trajectory always includes a straight line portion corresponding to the trajectory in the case of chest breathing, resulting in a bent shape. . Further, as shown in FIG. 38, a bending indicating how much a bent portion (approximate straight line LN2) is bent with respect to a straight line portion (approximate straight line LN1) corresponding to the locus in the case of chest breathing. The angle AG decreases when the abdominal breathing is shallow, and increases when the abdominal breathing is deep. Also, in the case of abdominal breathing, the trajectory of the Lissajous figure becomes smaller when breathing is shallow, and the trajectory of the Lissajous figure becomes larger when breathing is deep.

  Thus, the shape of the locus of the Lissajous figure is different between the chest breathing and the abdominal breathing. Further, the size and shape of the locus of the Lissajous figure changes depending on the magnitude (depth) of chest-type breathing and abdominal-type breathing. Therefore, the subject can look at the Lissajous figure to determine whether their current breathing is chest or abdominal breathing, or whether their current breathing is more of the chest or abdominal breathing. Can be grasped. In addition, the magnitude of chest breathing and abdominal breathing can be grasped from the Lissajous figure.

  In addition, when the subject performs exercises for chest breathing, the subject may respire consciously so that the locus of the Lissajous figure becomes an inclined straight line and the size thereof increases. Further, when abdominal breathing exercises are performed, breathing may be performed with an awareness that the locus of the Lissajous figure is bent and the size and bending angle AG are increased. If breathing training can be performed while looking at the Lissajous figure in this way, the training can be advanced while confirming whether or not chest breathing and abdominal breathing are correctly performed and their sizes as needed.

  In addition to chest-type breathing and abdominal-type breathing, there is a breathing method (hereinafter referred to as draw-in breathing) in which exhalation and inspiration are performed while maintaining a state in which the abdomen is recessed. In the case of draw-in breathing, as shown in FIG. 41, the bioelectrical impedance Za at the upper trunk and the bioelectrical impedance Zb at the middle trunk change in an increasing direction in inspiration, and the bioelectrical impedance Za in the upper trunk in exhalation and Both the bioelectrical impedance Zb in the middle of the trunk change in the decreasing direction. This change is the same as for chest breathing. This is because in the case of draw-in breathing, exhalation and inhalation are performed by chest breathing while maintaining a state where the abdomen is recessed. However, in the case of draw-in breathing, since the abdomen is pressed to dent the abdomen, the amplitude reference level of the bioelectrical impedance Zb in the middle of the trunk is higher than that in the case of the chest breathing as shown in FIG. Become. For this reason, when comparing the Lissajous figures in the case of draw-in breathing and chest breathing, as shown in FIG. 42, both trajectories are inclined straight lines, but bioelectrical impedance Zb in the middle of the trunk is assigned. The position of the locus is shifted in the other axial direction (in FIG. 42, the X-axis direction to which the third bioelectric impedance ZbR on the right side of the trunk is assigned).

  Therefore, the subject can grasp whether or not his / her respiration is a draw-in respiration by looking at the Lissajous figure. In the case of draw-in breathing, the trajectory of the Lissajous figure becomes smaller if the breathing is shallow, and the trajectory of the Lissajous figure becomes larger if the breathing is deep. Therefore, the magnitude of the draw-in breath can also be grasped from the Lissajous figure. Also, in the case of draw-in breathing, training can be carried out while confirming whether or not the draw-in breathing is correctly performed and the size thereof by performing training while looking at the Lissajous figure.

  When the first Lissajous figure for the right lung and the second Lissajous figure for the left lung can be displayed as described above, the subject can determine the type and size of his / her breathing, Whether or not abdominal breathing or draw-in breathing is correct can be determined for each of the left and right lungs. In addition, it is possible to objectively grasp the type and size of respiration, or whether chest respiration, abdominal respiration, and draw-in respiration are correctly performed based on the measured value of bioelectrical impedance. Further, by comparing the first Lissajous figure and the second Lissajous figure, it is possible to easily grasp the difference in the ventilation capacity between the left and right lungs.

  Further, by displaying two Lissajous figures for the right lung and the left lung, it becomes possible to perform breathing training for each of the left and right lungs. In the case of a healthy person, there is almost no difference in ventilation capacity between the left and right lungs. For example, a person with a disease in one lung has a large difference in ventilation capacity between the left and right lungs. Also, those who have experienced lung disease in the past may have differences in ventilation capacity between the left and right lungs. For example, if you want to increase the ventilation capacity of the left lung, such as when the ventilation capacity of the left lung is lower than the right lung, turn the left arm behind the right shoulder and push the left elbow back with the right hand to the left lung. By giving a load and breathing while maintaining this state, the ventilation ability of the left lung can be intensively trained.

  In addition, for example, in inductance-type respiratory plethysmography, a measurement band with a coil is wrapped around both the subject's thorax (sword-shaped projection) and abdomen (umbilical portion), and the change in the inductance of the coil results in the surroundings of the chest during breathing. The chest change rate Rrc (%) corresponding to the diameter change and the abdominal change rate Rabd (%) corresponding to the change in the peripheral diameter of the abdomen during breathing are measured. Among such inductance-type respiratory plethysmographs, for example, there is one that displays a Lissajous figure according to the Konno-Mead Diagram with the X axis as the abdominal change rate Rabd and the Y axis as the chest change rate Rrc.

  However, in the case of inductance-type respiratory plethysmography, measurement bands must be worn on the subject's chest and abdomen. In addition, when the subject is conscious of measurement or is nervous during measurement, the chest change rate Rrc and the abdomen change rate Rabd vary greatly. For this reason, a relatively reliable measurement result can be obtained during sleep, but there are many cases in which a highly reliable measurement result cannot be obtained when measurement is performed while the subject is awake.

  On the other hand, in the case of measurement by bioelectrical impedance, for example, if the limb induction eight electrode method is used, current electrodes and voltage electrodes may be disposed on both palms and soles, and current electrodes and voltages are applied to the trunk of the subject. Since there is no need to affix electrodes, there are few restrictions. In the case of bioelectrical impedance, for example, in the case of bioelectrical impedance Za at the upper part of the trunk, about 80% of the measured values are due to the inflow / outflow of air into the lungs and the remaining 20% are due to respiratory muscles or the like is there. Therefore, as compared with the case of inductance-type respiratory plethysmography, it is possible to reduce the influence of the subject being aware of the measurement or being nervous during the measurement, and obtain a more reliable measurement result. In addition to this, it is possible to measure with high sensitivity information directly related to breathing, such as air in and out of the lungs and vertical movement of the diaphragm.

For this reason, the Lissajous figure based on bioelectrical impedance reflects information directly related to breathing, such as air in / out of the lungs and the vertical movement of the diaphragm, with higher sensitivity than the Lissajous figure based on the inductance-type respiratory plethysmography. It will be. Further, as described above, the Lissajous figure obtained by inductance-type respiratory plethysmography has, for example, the X axis as the abdomen change rate Rabd and the Y axis as the chest change rate Rrc. In this case, the trajectory for one breath is a straight line that rises to the right in both cases of chest breathing and abdominal breathing. In addition, when the angle between the linear trajectory rising to the right and the X-axis is taken as the inclination angle of the trajectory, the inclination angle of the trajectory increases as the ratio of chest respiration increases and approaches 90 degrees. The higher the ratio is, the smaller the inclination angle of the trajectory approaches 0 degrees. In other words, in the case of a Lissajous figure based on inductance-type respiratory plethysmography, the shape of the trajectory is not different as in the present invention because the inclination of the trajectory changes only in the case of chest respiration and abdominal respiration. It is difficult to grasp the type of breathing from the figure.
The same applies to the case where a Lissajous figure conforming to the Konno-Mead Diagram is displayed using the chest circumference Rib and abdominal circumference Ab measured by respi tracing.

The display data generation unit (170) may generate display data for the first Lissajous figure and display data for the second Lissajous figure so that the first Lissajous figure and the second Lissajous figure are displayed in an overlapping manner. Good.
In this case, since the first Lissajous figure for the right lung and the second Lissajous figure for the left lung can be displayed in an overlapping manner, the difference in ventilation capacity between the left and right lungs can be easily grasped.

The display data generation unit (170) generates the display data of the first Lissajous figure and the display data of the second Lissajous figure so that the display modes of the locus of the first Lissajous figure and the locus of the second Lissajous figure are different. May be.
In this case, for example, even if the first Lissajous figure for the right lung and the second Lissajous figure for the left lung are displayed in an overlapping manner, the right lung and the left lung due to the difference in the display mode of the trajectory (for example, color and line type). Two Lissajous figures for the lung can be easily distinguished.

Further, a trajectory analysis unit (170) for detecting a difference between the trajectory of the first Lissajous figure and the trajectory of the second Lissajous figure is further provided, and the display data generation unit (170) displays the difference in an emphasized manner. Display data for the first Lissajous figure and display data for the second Lissajous figure may be generated.
Even in this way, it is possible to easily grasp the difference in ventilation capacity between the left and right lungs.

In addition, a first amplitude value indicating the amplitude of the measured value of the first bioelectrical impedance (ZaR), a second amplitude value indicating the amplitude of the measured value of the second bioelectrical impedance (ZaL), and a third bioelectrical impedance ( An amplitude value specifying unit (170) for specifying a third amplitude value indicating the amplitude of the measured value of ZbR) and a fourth amplitude value indicating the amplitude of the measured value of the fourth bioelectrical impedance (ZbL); The data generator (170) adjusts the range of one axis using the first amplitude value and the second amplitude value, and adjusts the range of the other axis using the third amplitude value and the fourth amplitude value. The display data of the first Lissajous figure and the display data of the second Lissajous figure may be generated.
In this case, by adjusting the two-axis range, the Lissajous figure display area for displaying the Lissajous figure is exactly the right size for the first Lissajous figure for the right lung and the second Lissajous figure for the left lung. Can be displayed. Two Lissajous figures can also be displayed at the center of the Lissajous figure display area. This makes it easy to see the Lissajous figure.

  In addition, a first amplitude value indicating the amplitude of the measured value of the first bioelectrical impedance (ZaR), a second amplitude value indicating the amplitude of the measured value of the second bioelectrical impedance (ZaL), and a third bioelectrical impedance ( An amplitude value specifying unit (170) for specifying a third amplitude value indicating the amplitude of the measured value of ZbR) and a fourth amplitude value indicating the amplitude of the measured value of the fourth bioelectrical impedance (ZbL); The data generation unit (170) uses the first amplitude value and the second amplitude value as the processing to be performed when generating the display data of the first Lissajous figure and the display data of the second Lissajous figure. A first range adjustment process to be adjusted, and a second range adjustment process to adjust the range of the other axis using the third amplitude value and the fourth amplitude value, and the frequency of performing the second range adjustment process is first. Range adjustment processing It may be less than the frequency of performing.

Comparing the Lissajous figures in the case of draw-in breathing and chest breathing, as shown in FIG. 42, both trajectories are inclined straight lines, but the other part to which the bioelectrical impedance Zb of the middle trunk is assigned. The position of the locus is shifted in the axial direction (in FIG. 42, the X-axis direction to which the third bioelectric impedance ZbR on the right side of the trunk is assigned). Here, if the display position is frequently adjusted by the first range adjustment process or the second range adjustment process, two Lissajous figures are always displayed in the center of the Lissajous figure display area. You will not be able to tell the chest breath.
According to the above aspect, for example, the first range adjustment process is performed for each breath, while the second range adjustment process is performed only once for the first time and is not performed thereafter. However, since the frequency of performing the second range adjustment process is reduced, the position of the locus of the Lissajous figure is shifted in the other axial direction in the case of the draw-in breathing and the case of the chest breathing. This makes it possible to distinguish between draw-in breathing and chest breathing from the Lissajous figure. Moreover, the power consumption of the respiration level measuring device can be reduced by the amount that the frequency of performing the second range adjustment process is reduced. In addition, although the frequency is low, the second range adjustment processing is also performed, so that two Lissajous figures for the right lung and the left lung are displayed in the right size with respect to the Lissajous figure display area for easy viewing. be able to.

Moreover, as an aspect of the respiratory level measurement apparatus (1) according to the present invention, one of two axes orthogonal to each other is a first bioelectrical impedance (ZaR) and the other axis is a third bioelectrical impedance (ZbR). Display data of a Lissajous figure (FIG. 45: for the right lung) showing a change over time of the measured value of the first bioelectrical impedance and the measured value of the third bioelectrical impedance, or one axis as the second bioelectrical impedance (ZaL), the other axis is the fourth bioelectrical impedance (ZbL), and the Lissajous figure showing the time course of the measured value of the second bioelectrical impedance and the measured value of the fourth bioelectrical impedance (FIG. 45: for the left lung ) Display data generation unit (170) may be further included.
As described above, either the Lissajous figure for the right lung or the Lissajous figure for the left lung may be displayed.

In this case, the display data generation unit (170) may generate the display data of the Lissajous figure so that the display mode of the locus of the Lissajous figure is different between the latest one breath and the other past breaths.
For example, as shown in FIGS. 39 and 40, in the case of a Lissajous figure that continuously shows the state of breathing a plurality of times, if the locus display mode is the same, it is difficult to grasp the latest locus for one breath. If it is the above-mentioned aspect, the latest locus | trajectory for one breath can be easily grasped | ascertained from the difference in a display aspect (for example, a color, a line type, etc.).

The display data generation unit (170) may generate the display data of the Lissajous figure so that the display mode of the locus of the Lissajous figure changes according to the elapsed time.
For example, if the color of the trajectory becomes lighter as the elapsed time increases, the new trajectory becomes darker because the color of the new trajectory becomes darker, so that a new trajectory such as the latest trajectory for one breath can be easily grasped.

Further, the display data generation unit (170) generates the display data of the Lissajous figure and generates the display data of the Lissajous figure for breathing guidance according to the target breathing type and the magnitude of the breathing. Good.
In this case, in addition to the Lissajous figure indicating the breathing state of the subject, it is possible to display a Lissajous figure for breathing guidance indicating the target breathing state. Therefore, the subject can perform breathing training while comparing both Lissajous figures. In this case, the subject can acquire the target breath by consciously breathing so that the locus of the Lissajous figure indicating the state of his / her breathing matches the locus of the Lissajous figure for breathing guidance. . Thus, by using the Lissajous figure for breathing guidance, the subject's breathing can be effectively taught.

  Note that the display data generation unit (170) may generate display data of both so that a Lissajous figure indicating the breathing state of the subject and a Lissajous figure for breathing guidance are displayed in an overlapping manner. In this way, the difference from the target breath can be easily grasped. Further, the display data generation unit (170) may generate both display data so that the display form of the Lissajous figure showing the breathing state of the subject and the Lissajous figure for breathing guidance are different in display mode. Good. In this way, for example, even if the Lissajous figure indicating the breathing state of the subject and the Lissajous figure for breathing guidance are displayed in an overlapping manner, both of them can be easily displayed due to the difference in the display mode of the trajectory (for example, color and line type). Can be distinguished.

In addition, the inclination angle calculation unit (170) that calculates the inclination angle of the locus of the Lissajous figure and the inclination angle calculated by the inclination angle calculation unit are compared with a predetermined reference inclination angle to determine whether the lung ventilation ability is good or bad. And a ventilation capacity determination unit (170) for determination.
In this case, the quality of the lung ventilation ability can be easily determined from the locus of the Lissajous figure. Note that the inclination angle of the locus of the Lissajous figure varies depending on the posture at the time of measurement, such as standing, sitting, and the supine position, so the reference inclination angle also differs depending on the posture at the time of measurement.

In addition, as an aspect of the respiratory level measurement device (1) according to the present invention, for each class determined according to the breathing ability, a training menu for training breathing, and a clear condition for clearing the class A respiration capability detection unit (170) for detecting the respiration ability of the subject based on the measurement result of the bioelectrical impedance measurement unit or the calculation result of the respiration level calculation unit, and the storage unit Refer to and identify the class according to the breathing ability detected by the breathing ability detection unit, perform a process for training the subject's breathing based on the training menu corresponding to the identified class, and correspond to the identified class When the clear condition is satisfied, a training management unit (170) that shifts the class of the subject to the next class higher than the class may be further provided.
In this case, the subject can perform breathing training based on a training menu corresponding to his / her breathing ability. In addition, the training menu is prepared for each class, and by having the game characteristics of proceeding to the next class while clearing each class, it is possible to perform breathing training while having fun, so subjects for breathing training You can also increase your motivation.

In order to solve the above-described problem, the respiratory level measuring device (300) according to the present invention includes a bioelectrical impedance measured by the bioelectrical impedance measuring device (200 ′) and a portion including the right lung of the subject, and the subject. The right lung respiration level indicating the ventilation capacity of the right lung is obtained based on the input unit (320) for inputting the bioelectric impedance of the part including the left lung and the measurement value of the bioelectric impedance of the part including the right lung. On the other hand, a respiration level calculation unit (360) for obtaining a left lung respiration level indicating the ventilation capacity of the left lung based on a measurement value of bioelectrical impedance of a part including the left lung is provided.
Also in the respiratory level measuring apparatus having the above configuration, the ventilation ability of each of the subject's right lung and left lung can be accurately and easily measured. The respiratory level measurement device may be, for example, a game machine, a personal computer, or a portable electronic device (for example, a mobile phone).

In order to solve the above-described problem, a respiration level measurement system (5) according to the present invention includes a bioelectrical impedance measuring unit that measures bioelectrical impedances of a part including the right lung and a part including the left lung of a subject. (200 ′, 360) and the measurement value of the bioelectrical impedance of the region including the right lung, while obtaining the right lung respiration level indicating the ventilation ability of the right lung, while measuring the bioelectrical impedance of the region including the left lung A respiration level calculation unit (300, 360) for obtaining a left lung respiration level indicating the ventilation capacity of the left lung based on the value.
Even in the respiratory level measurement system having the above configuration, the ventilation ability of each of the right lung and left lung of the subject can be accurately and easily measured. Note that the respiration level measurement system may be configured using, for example, a game machine, a personal computer, a portable electronic device, or the like.

It is a block diagram shown about the electric composition of the living body measuring device concerning a 1st embodiment of the present invention. It is a perspective view which shows the example of an external appearance of a biometric apparatus. It is explanatory drawing which shows electrode arrangement | positioning of a biometric apparatus. It is explanatory drawing for demonstrating selection of a current electrode and selection of a voltage electrode. It is a flowchart which shows the operation | movement content of a biometric apparatus. It is a schematic diagram which shows the outline of the structure | tissue which comprises a trunk. It is a circuit diagram which shows the equivalent circuit of the bioelectrical impedance of a trunk. It is explanatory drawing explaining the relationship between respiration and the change of bioelectrical impedance. It is a figure which shows the change of the bioelectrical impedance in abdominal respiration. It is a figure which shows the change of the bioelectrical impedance in chest type respiration. It is a circuit diagram which shows the equivalent circuit of the bioelectrical impedance of the trunk upper part. It is a flowchart which shows the processing content of a respiration level detection process. It is a flowchart which shows the processing content of a 1st centering process. It is a flowchart which shows the processing content of a respiration timing extraction process. It is a flowchart which shows the processing content of a respiration timing extraction process. It is a flowchart which shows the processing content of a breathing speed discrimination | determination flag setting process. It is a flowchart which shows the processing content of a 1st centering value extraction process. It is a figure which shows the time-dependent change of the 1st relative value and 2nd relative value accompanying a test subject's respiration. It is a flowchart which shows the processing content of a 1st right lung respiration level extraction process. It is a flowchart which shows the processing content of a 1st zero cross timing determination process. It is a figure which shows the display mode in a display part. It is a flowchart which shows the processing content of the respiration level detection process in 2nd Embodiment of this invention. It is a flowchart which shows the processing content of the respiration level detection process in 2nd Embodiment of this invention. It is a schematic diagram for demonstrating conceptually the production | generation method of a 3rd centering value. It is a flowchart which shows the processing content of a 3rd relative value calculation process. It is a flowchart which shows the processing content of a 2nd right lung respiration level extraction process. It is a figure which shows the display mode in a display part. It is a figure which shows the circumference change of the chest and abdomen accompanying abdominal respiration. It is a figure which shows the circumference diameter change of the chest and abdomen accompanying chest type respiration. It is a correlation diagram showing the relationship between the ratio of the change in the circumference of the chest and the change in the circumference of the abdomen, the relative information of the bioelectrical impedance of the upper trunk and the relative information of the bioelectrical impedance of the middle trunk. It is a flowchart which shows the processing content of the respiration level detection process in 3rd Embodiment of this invention. It is a flowchart which shows the processing content of the respiration level detection process in 3rd Embodiment of this invention. It is a flowchart which shows the processing content of (DELTA) Rib / (DELTA) Ab estimation calculation processing. It is a flowchart which shows the processing content of (DELTA) Rib / (DELTA) Ab estimation calculation processing. It is a figure which shows the calculation result of (DELTA) Rib / (DELTA) Ab estimation calculation processing. It is a figure which shows the display mode in a display part. It is a figure which shows the Lissajous figure for 1 breath (for right lungs) in the case of chest type breathing. It is a figure which shows the Lissajous figure for 1 breath (for right lungs) in the case of abdominal respiration. It is a figure which shows the Lissajous figure (for right lungs) for several times of breathing in the case of chest type breathing. It is a figure which shows the Lissajous figure (for right lungs) for several times of breathing in the case of abdominal breathing. It is a graph which shows the time change of the bioelectrical impedance of a trunk upper part and a trunk trunk. It is a figure which shows the Lissajous figure (for right lung) in the case of draw-in respiration and the case of chest respiration. It is a flowchart which shows the processing content of a Lissajous figure display process. It is a figure for demonstrating the change of the Lissajous figure from chest type breathing to abdominal type breathing. It is a figure which shows the case where two Lissajous figures (for 1 breath) for right lung and left lung are displayed superimposed. It is a figure which shows the case where the difference of two Lissajous figures for right lung and left lung is highlighted. It is a figure which shows the case where the average value of two Lissajous figures for right lung and left lung is plotted. It is a figure which shows a Lissajous figure at the time of switching X axis and Y axis. It is a figure for demonstrating the change from the chest type | mold breathing to abdominal type | mold breathing in the Lissajous figure at the time of switching an X-axis and a Y-axis. It is a schematic diagram for demonstrating the method of centering the display position of two Lissajous figures for right lung and left lung. It is a figure which shows a Lissajous figure at the time of changing the color of the color of a locus | trajectory with the latest one breath and other past breaths. It is FIG. (1) for demonstrating the assist display by a Lissajous figure. It is FIG. (2) for demonstrating the assist display by a Lissajous figure. It is FIG. (1) for demonstrating the method to determine the quality of the ventilation capability of a lung. It is FIG. (2) for demonstrating the method to determine the quality of the ventilation capability of a lung. It is FIG. (3) for demonstrating the method to determine the quality of the ventilation capability of a lung. It is a figure which shows the display mode in the modification (3) of this invention. It is a figure which shows an example of the display mode which alert | reports the magnitude | size of respiration. It is a figure which shows the structure of the biometric system using a home game machine. It is a block diagram which shows the structure of a game machine. It is a figure which shows the data structure of a training menu management table. It is a flowchart which shows the processing content of a breathing exercise management process. It is a flowchart which shows the processing content of the respiration classification discrimination | determination process (for trunk right side).

<A: First Embodiment>
<A-1: Configuration of biometric apparatus>
FIG. 1 is a block diagram showing a configuration of a biometric apparatus 1 according to the first embodiment of the present invention. The living body measuring apparatus 1 measures the state of a living body, and a part of the function of the living body measuring apparatus 1 plays a role as a device for measuring the right lung ventilation ability and the left lung ventilation ability of the subject.

  The biometric apparatus 1 includes a management unit 100 that measures body weight and manages the operation of the entire apparatus, and a bioelectrical impedance measurement unit 200 that measures bioelectrical impedance of each part of the subject. The management unit 100 includes a weight scale 110, a first storage unit 120, a second storage unit 130, a sound processing unit 140, a speaker 145, an input unit 150, and a display unit 160. These components are connected to a CPU (Central Processing Unit) 170 via a bus. The CPU 170 functions as a control center that controls the entire apparatus. The CPU 170 operates by receiving a clock signal from a clock signal generation circuit (not shown). Further, when a power switch (not shown) is turned on to each component, power is supplied from the power supply circuit.

  The weight scale 110 measures the weight of the subject, and outputs the measured weight data to the CPU 170 via the bus. The first storage unit 120 is a non-volatile memory, and is composed of, for example, a ROM (Read Only Memory). The first storage unit 120 stores a control program for controlling the entire apparatus. CPU 170 executes a predetermined calculation according to the control program.

  The second storage unit 130 is a volatile memory, and includes, for example, a DRAM (Dynamic Random Access Memory) or the like. The second storage unit 130 functions as a work area of the CPU 170, and stores data when the CPU 170 executes a predetermined calculation. In addition, the audio processing unit 140 amplifies an audio signal obtained by DA converting audio data under the control of the CPU 170 and outputs the amplified audio signal to the speaker 145. The speaker 145 converts the amplified audio signal into vibration and emits the sound. Thus, advice information such as guidance on the breathing method can be notified to the subject by sound.

  The input unit 150 includes various switches, and when a subject operates the switches, information such as height, age, and sex is input. The display unit 160 displays a measurement result such as weight and type of breath, a function for notifying advice information such as a rhythm and a pattern of exhalation and inspiration for leading to abdominal breathing, or a message prompting the subject to input various information. It has the function to do. The display unit 160 is configured by, for example, a liquid crystal display device.

Next, the bioelectrical impedance measuring unit 200 measures the bioelectrical impedance of the subject (human body). The bioelectrical impedance measurement unit 200 includes an alternating current output circuit 210, a reference current detection circuit 220, a potential difference detection circuit 230, an A / D converter 240, and electrode switching circuits 251 and 252.
The alternating current output circuit 210 is a means for generating a reference current Iref. The alternating current output circuit 210 generates the reference current Iref so that the effective value of the reference current Iref becomes a predetermined value. The reference current detection circuit 220 detects the magnitude of the reference current Iref flowing through the object to be measured and outputs it as current data Di to the CPU 170 and energizes the subject with the reference current Iref. In this case, the electrode switching circuit 252 selects two of the current electrodes X1 to X4 and supplies current.
Further, the potential difference detection circuit 230 detects a potential difference between two voltage electrodes selected from the voltage electrodes Y1 to Y4 and generates a potential difference signal ΔV. The A / D converter 240 converts the potential difference signal ΔV from an analog signal to a digital signal and outputs it to the CPU 170 as voltage data Dv. The CPU 170 calculates a bioelectric impedance Z (= Dv / Di) based on the voltage data Dv and the current data Di.

The first storage unit 120 can store various data in advance. For example, a correlation equation or a correlation table for calculating body fat fat percentage and muscle mass using the bioelectrical impedance of each part as a variable is stored.
The CPU 170 calculates body weight, bioelectrical impedance (for example, upper limb bioelectrical impedance, lower limb bioelectrical impedance, trunk bioelectrical impedance) of various parts of the subject, and various input / output, measurement, calculation, and the like. Control. Based on bioelectrical impedance, etc., visceral fat / subcutaneous fat, visceral fat mass, subcutaneous fat percentage, subcutaneous fat mass, whole body fat percentage, fat percentage of each part of body (upper limb fat percentage, lower limb fat percentage, body Stem fat percentage etc.) can also be calculated.

  In FIG. 2, the example of an external appearance of the biometric apparatus 1 is shown. The biometric device 1 has an L-shape and includes a columnar casing 30 on the pedestal 20. The pedestal 20 is provided with a current electrode X1 and a voltage electrode Y1 for the left foot, and a current electrode X2 and a voltage electrode Y2 for the right foot. A display unit 160 is provided on the upper portion of the housing unit 30. The display unit 160 is configured with a touch panel and also functions as the input unit 150. Further, left and right electrode portions 30 </ b> L and right hand electrode portions 30 </ b> R are provided on the left and right side surfaces of the housing portion 30.

  FIG. 3 is an enlarged view in which the upper part of the housing part 30 is enlarged. As shown in this figure, the left-hand electrode portion 30L includes a current electrode X3 and a voltage electrode Y3, and the right-hand electrode portion 30R includes a current electrode X4 and a voltage electrode Y4. The subject performs measurement by standing on the pedestal 30 and holding the electrode part 30L and the electrode part 30R with the left and right hands lowered.

  The electrode switching circuits 251 and 252 select eight electrodes to be worn on both hands and both feet under the control of the CPU 170. By appropriately selecting these eight electrodes, it is possible to measure the bioelectrical impedance Z at a predetermined part of the human body. For example, as shown in FIG. 4A, the reference current Iref is supplied between the current electrode X1 for the left foot and the current electrode X3 for the left hand, and the voltage electrode Y1 for the left foot and the voltage electrode Y3 for the left hand If the potential difference is measured between them, the bioelectrical impedance of the whole body can be measured. Note that the bioelectric impedance of the whole body can be measured even if the reference current Iref is passed between the current electrodes X2 and X4 and the potential difference between the voltage electrodes Y2 and Y4 is measured. Furthermore, as shown in FIG. 4 (K), both palms may be short-circuited, both feet may be short-circuited, and the bioelectric impedance from both palms to both feet may be measured as the bioelectric impedance of the whole body.

  Further, as shown in FIG. 4B, the reference current Iref is supplied between the right foot current electrode X2 and the right hand current electrode X4, and the right foot voltage electrode Y2 and the left foot voltage electrode Y1 are connected. If the potential difference is measured between them, the bioelectrical impedance Z of the right lower limb can be measured. Further, as shown in FIG. 4C, the reference current Iref is supplied between the left foot current electrode X1 and the left hand current electrode X3, and the left foot voltage electrode Y1 and the right foot voltage electrode Y2 are connected. If the potential difference is measured between them, the bioelectrical impedance Z of the left lower limb can be measured.

  Further, as shown in FIG. 4D, the reference current Iref is supplied between the right-hand current electrode X4 and the right-foot current electrode X2, and the right-hand voltage electrode Y4 and the left-hand voltage electrode Y3 are connected. By measuring the potential difference between them, the bioelectrical impedance Z of the upper right limb (upper trunk) can be measured. However, the present invention is not limited thereto, and the reference current Iref is supplied between the left-hand current electrode X3 and the right-hand current electrode X4, and the potential difference between the right-hand voltage electrode Y4 and the right-foot voltage electrode Y2 is determined. The bioelectric impedance Z of the upper right limb (upper trunk) can also be measured by measuring.

  Further, as shown in FIG. 4E, the reference current Iref is supplied between the left-hand current electrode X3 and the left-foot current electrode X1, and the right-hand voltage electrode Y4 and the left-hand voltage electrode Y3 are connected. If the potential difference is measured between them, the bioelectrical impedance Z of the left upper limb (upper trunk) can be measured. However, the reference current Iref is supplied between the left-hand current electrode X3 and the right-hand current electrode X4, and the potential difference between the left-hand voltage electrode Y3 and the left-foot voltage electrode Y1 is not limited thereto. The bioelectrical impedance Z of the left upper limb (upper trunk) can also be measured by measuring.

  Further, as shown in FIG. 4F, the reference current Iref is supplied between the right-hand current electrode X4 and the left-hand current electrode X3, and the right-hand voltage electrode Y4 and the left-hand voltage electrode Y3 are connected. If the potential difference is measured between the two, the bioelectric impedance Z between both palms can be measured. Here, when the trunk is divided into the upper trunk and the middle trunk, the bioelectrical impedance between the left upper limb, the upper right limb, and the palm includes the upper trunk. For this reason, it is also possible to handle the bioelectric impedance between the left upper limb, the upper right limb, and the palm as the bioelectric impedance of the upper trunk.

  Further, as shown in FIG. 4G, the reference current Iref is supplied between the left hand current electrode X3 and the left foot current electrode X1, and the right hand voltage electrode Y4 and the right foot voltage electrode Y2 are connected. If the potential difference is measured between the two, the bioelectrical impedance in the middle of the trunk can be measured. Further, as shown in FIG. 4H, the reference current Iref is supplied between the right-hand current electrode X4 and the right-foot current electrode X2, and the left-hand voltage electrode Y3 and the left-foot voltage electrode Y1 are connected. If the potential difference is measured between the two, the bioelectrical impedance in the middle of the trunk can be measured. Further, as shown in FIG. 4 (I), the reference current Iref is supplied between the current electrode X4 for the right hand and the current electrode X1 for the left foot, and the voltage electrode Y3 for the left hand and the voltage electrode Y2 for the right foot By measuring the potential difference between the two, it is possible to measure the bioelectrical impedance that crosses the middle part of the trunk diagonally. As shown in FIG. 4J, the reference current Iref is supplied between the current electrode X2 for the right foot and the current electrode X3 for the left hand, and between the voltage electrode Y4 for the right hand and the voltage electrode Y1 for the left foot. By measuring the potential difference, bioelectrical impedance that crosses the middle of the trunk diagonally can be measured.

  The method for measuring the bioelectrical impedance Zx of the trunk is not limited to the above-described method, and an electrode for supplying a reference current Iref and an electrode for detecting a potential difference are appropriately selected from the electrodes of both hands and feet. Thus, the bioelectrical impedance Z of each part of the human body such as the hand, foot, or whole body is measured, and the bioelectrical impedance Z of the middle trunk is calculated by adding and subtracting the measurement results. Further, the bioelectrical impedance Zx of the trunk can be measured even if the earlobe of the head is used as a substitute for any of the limbs in addition to the limbs. In addition, it goes without saying that a contact electrode is provided on the trunk.

<A-2: Operation of biometric apparatus>
FIG. 5 is a flowchart showing the operation of the biometric apparatus 1. First, when a power switch (not shown) in the input unit 150 is turned on, power is supplied to each part of the electric system from a power supply unit (not shown), and body identification information including height (height, gender, age) is displayed on the display unit 160. Etc.) is displayed (step S1).
Subsequently, when height, sex, age, and the like are input from the input unit 150, the weight is measured by the weight scale 110, and the CPU 170 acquires the weight (step S2).

  After step S2, CPU 170 executes a respiration level detection process (step S3). In this process, the CPU 170 obtains a right lung respiration level indicating the ventilation ability of the subject's right lung and a left lung respiration level indicating the ventilation ability of the subject's left lung. Details of this will be described later. After step S3, the CPU 170 executes a breathing level display process for displaying the right lung breathing level and the left lung breathing ability in the one breath for each breath of the subject (step S4).

<A-3: Principle of respiratory level detection>
Next, the principle of respiratory level detection will be described. FIG. 6 is a schematic diagram showing an outline of the tissue of the trunk. As shown in FIG. 6, the trunk tissue is divided into upper and lower portions by a diaphragm. In the upper part, lungs and thoracic skeletal muscles such as internal and external intercostals are formed. On the other hand, a visceral tissue and abdominal skeletal muscles including internal and external oblique / lateral abdominal muscles and rectus abdominis muscles are formed in the lower part.
In both abdominal breathing and chest breathing, the diaphragm rises and the lungs are compressed during expiration, and the diaphragm descends and the lungs expand and expand during inspiration. A feature of abdominal breathing that does not exist in chest breathing is that the diaphragm is moved up and down along with the visceral tissues by expansion and contraction of abdominal respiratory muscles such as the rectus abdominis, internal and external oblique and transverse abdominal muscles.

  Here, the bioelectric impedance Za of the upper trunk and the bioelectric impedance Zb of the middle trunk can be represented by an equivalent circuit shown in FIG. As shown in FIG. 7, the bioelectrical impedance Za of the upper trunk is composed of the bioelectrical impedance Z1 of the thoracic skeletal muscle, the parallel impedance of the pulmonary bioelectrical impedance Z2, and the bioelectrical impedance Z3 of the upper limb skeletal muscle in series. Will be connected to. Here, the parallel impedance of Z1 and Z2 corresponds to the bioelectrical impedance of the upper lobe of the lung.

  Further, as shown in FIG. 7, the bioelectrical impedance Zb of the middle trunk includes the bioelectrical impedance Z4 of the thoracic skeletal muscle, the parallel impedance of the bioelectrical impedance Z5 of the lung, and the bioelectrical impedance Z6 of the abdominal skeletal muscle, In addition, the parallel impedance of the bioelectric impedance Z7 of the visceral tissue is connected in series. Here, the parallel impedance of Z4 and Z5 corresponds to the bioelectrical impedance of the middle and lower lobe of the lung. Further, the bioelectric impedance of the diaphragm can be considered to be included in the bioelectric impedance Z7 typified by visceral tissue.

  Next, with reference to FIG. 8, the relationship between respiration and changes in bioelectrical impedance will be described. It is considered that the change in the bioelectrical impedance Za linked to respiration is mainly caused by a change in electrical characteristics (electric conductivity, 1 / volume resistivity) due to the entry and exit of highly insulating air into and from the lungs. That is, in exhalation (exhalation), the amount of air contained in the lung tissue decreases, so that the bioelectric impedance Z2 of the lung changes in a decreasing direction (ΔZlu <0). On the other hand, in the inspiration (inhalation), the amount of air increases, so that the bioelectric impedance Z2 of the lung changes in the increasing direction (ΔZlu> 0).

  In the breathing method (thoracic breathing) that expands the thorax with the chest type, the expansion and contraction of the respiratory skeletal muscles such as the internal and external intercostal muscles and the expansion and contraction of the lungs act in the same direction, so if the lung bioelectrical impedance Z2 increases, the chest The bioelectrical impedance Z1 of the skeletal muscle also increases, and if the bioelectrical impedance Z2 of the lung decreases, the bioelectrical impedance Z1 of the thoracic skeletal muscle also decreases. On the other hand, since abdominal breathing is a breathing method in which changes in the rib cage are hardly seen, the bioelectrical impedance Z1 of the thoracic skeletal muscle hardly changes, and the bioelectrical impedance Z2 of the lung changes greatly with respiration. The bioelectrical impedance Za includes the bioelectrical impedance Z3 of the upper limb skeletal muscle, but the upper limb skeletal muscle is not a muscle that directly contributes to respiration. In the present embodiment, the subject stands on the pedestal portion 20 of the measuring apparatus shown in FIG. 2 and grasps 30L and 30R in a state where the left and right arms are lowered, so the upper limb skeletal muscle (Z3) is measured during the measurement. Rarely moves. As shown in FIG. 9 and FIG. 10, the bioelectrical impedance Za of the upper trunk changes in the increasing direction in the inspiration, regardless of whether the subject is breathing or abdominal breathing. The bioelectrical impedance Za at the upper trunk changes in a decreasing direction.

  As described above, the bioelectric impedance Za of the upper trunk includes the bioelectric impedance of the upper right limb and the bioelectric impedance of the left upper limb. In the present embodiment, the bioelectric impedance of the upper right limb is expressed as a first bioelectric impedance ZaR, and the bioelectric impedance of the left upper limb is expressed as a second bioelectric impedance ZaL. Here, the first bioelectric impedance ZaR of the upper right limb and the second bioelectric impedance ZaL of the left upper limb can be represented by an equivalent circuit shown in FIG.

  As shown in FIG. 11, the first bioelectrical impedance ZaR is composed of the bioelectrical impedance Z1R of the right thoracic skeletal muscle, the parallel impedance of the bioelectrical impedance Z2R of the right lung, and the bioelectrical impedance Z3R of the right upper limb skeletal muscle. It will be connected in series. The parallel impedance of Z1R and Z2R corresponds to the bioelectrical impedance of the upper lobe of the right lung. That is, the first bioelectrical impedance ZaR is the bioelectrical impedance of the upper right side of the trunk including the upper part of the subject's right lung and not including the abdomen.

  The first bioelectrical impedance ZaR changes as air enters and exits the right lung with breathing. The change is the same as the bioelectrical impedance Za of the upper trunk, but the amplitude of the first bioelectrical impedance ZaR increases as the amount of air entering and exiting the right lung, that is, the amount of ventilation in the right lung increases. Also grows. In the present embodiment, focusing on the fact that the amplitude value of the first bioelectrical impedance ZaR is a value corresponding to the ventilation capacity of the upper part of the right lung, based on the measured value of the first bioelectrical impedance ZaR, A first right lung respiratory level BR1 indicating the upper ventilation capacity is determined. Details of this will be described later.

  Further, as shown in FIG. 11, the second bioelectric impedance ZaL of the left upper limb is the parallel impedance of the bioelectric impedance Z1L of the left chest skeletal muscle and the bioelectric impedance Z2L of the left lung, and the living body of the left upper limb skeletal muscle. The electrical impedance Z3L is connected in series. The parallel impedance of Z1L and Z2L corresponds to the bioelectrical impedance of the upper lobe of the left lung. That is, the second bioelectrical impedance ZaL is the bioelectrical impedance of the upper left side of the trunk including the upper part of the subject's left lung and not including the abdomen.

  The second bioelectrical impedance ZaL changes as air enters and leaves the left lung with breathing. The change is similar to the bioelectrical impedance Za of the upper trunk, but the amplitude of the second bioelectrical impedance ZaL increases as the amount of air flowing into and out of the left lung, that is, the amount of ventilation in the left lung increases. Also grows. In the present embodiment, focusing on the fact that the amplitude value of the second bioelectrical impedance ZaL is a value corresponding to the ventilation capacity of the upper part of the left lung, based on the measured value of the second bioelectrical impedance ZaL, A first left lung respiration level BL1 indicating the upper ventilation capacity is determined. Details of this will be described later.

  On the other hand, the change in the bioelectrical impedance Zb in the middle trunk due to respiration is linked with the movement of the diaphragm. As described above, in both cases of abdominal breathing and chest breathing, the diaphragm rises during expiration and falls during inspiration. A feature of abdominal breathing is that the diaphragm is moved up and down together with the visceral tissue by expansion and contraction of the abdominal respiratory muscles. More specifically, only during expiration of abdominal breathing, the bioelectrical impedance of the parallel part of the visceral tissue and the abdominal skeletal muscle increases by tensioning the abdominal muscles and pushing up the diaphragm along with the visceral tissue ( ΔZst> 0). At this time, the bioelectrical impedance of the lung tissue decreases (ΔZlu <0). For this reason, it acts so that the increase in the bioelectric impedance in the upper part from the diaphragm cancels the increase in the bioelectric impedance in the lower part from the diaphragm. Thus, the movements of the abdominal skeletal muscle and the visceral tissue below the diaphragm differ between the chest breathing and the abdominal breathing.

  As shown in FIG. 9, when the breathing of the subject is abdominal breathing, the bioelectrical impedance Zb in the middle trunk changes in the increasing direction by inhalation, while the decrease of the bioelectrical impedance from the diaphragm to the upper part of the exhalation changes from the diaphragm. Since the increase in the lower bioelectric impedance acts to cancel, the bioelectric impedance Zb in the middle trunk changes in the increasing direction. In addition, as shown in FIG. 10, when the subject's breathing is chest-type breathing, the bioelectrical impedance Zb in the middle trunk is increased in the inspiration, similarly to the change in the bioelectrical impedance Za in the upper trunk. On the other hand, in exhalation, the bioelectrical impedance Zb in the middle of the trunk changes in a decreasing direction.

<A-4: Respiration level detection process>
Next, a respiration level detection process executed by the CPU 170 will be described. FIG. 12 is a flowchart for explaining specific contents of the respiration level detection process. In the present embodiment, it is set so that 10 breathing level detection processes are executed for one normal breathing (= one breathing + 1 breathing). Here, it is assumed that the time required for one normal breath is 4 seconds, and the CPU 170 executes the breath level detection process every 0.4 seconds. Below, the timing (timing for every 0.4 second) which performs a respiration level detection process is called sampling timing. This is an example, and the timing for executing the respiration level detection process can be arbitrarily set.

  As shown in FIG. 12, first, the CPU 170 determines whether or not the sampling timing has been reached (step S10), and proceeds to step S20 if the result of step S10 is affirmative. Here, assuming the case where the nth (n ≧ 1) sampling timing has been reached, the specific contents of each step after step S20 will be described. Prior to specific description of each step after step S20, first, an outline of the contents of each step will be briefly described.

  As shown in FIG. 12, in step S20 after step S10, the CPU 170 measures the first bioelectric impedance ZaR on the upper right side of the trunk (upper right limb). In step S30 after step S20, the CPU 170 measures the second bioelectrical impedance ZaL of the upper left trunk (left upper limb). In step S40 after step S30, the CPU 170 performs a smoothing process on each of the first bioelectrical impedance ZaR measured in step S20 and the second bioelectrical impedance ZaL measured in step S30. In step S50 after step S40, the CPU 170 generates a first centering value ZaR0 indicating the amplitude reference level of the measured value of the first bioelectrical impedance ZaR. The first centering value ZaR0 indicates an amplitude reference level for extracting information resulting from respiration from a waveform indicating a temporal change in the first bioelectrical impedance ZaR. In step S60 after step S50, the CPU 170 generates a second centering value ZaL0 indicating the amplitude reference level of the measured value of the second bioelectrical impedance ZaL. The second centering value ZaL0 indicates an amplitude reference level for extracting information resulting from respiration from a waveform indicating a temporal change in the second bioelectrical impedance ZaL. In step S70 after step S60, the CPU 170 calculates a first relative value ΔZaR that is a relative value of the measured value of the first bioelectrical impedance ZaR with respect to the first centering value ZaR0. In step S80 after step S70, the CPU 170 calculates a second relative value ΔZal which is a relative value of the measured value of the second bioelectrical impedance ZaL with respect to the second centering value ZaL0. In step S90 after step S80, the CPU 170 executes a first right lung respiration level extraction process for extracting a first right lung respiration level BR1 indicating the ventilation capacity of the upper part of the right lung. Further, in step S100 after step S90, the CPU 170 executes a first left lung respiration level extraction process for extracting a first left lung respiration level BL1 indicating the ventilation capacity of the upper part of the left lung. . Hereinafter, the specific contents of each step will be described in order.

  As shown in FIG. 12, in step S20, the CPU 170 measures the first bioelectric impedance ZaR on the upper right side of the trunk. For example, the CPU 170 controls the electrode switching circuit 252 so as to select the current electrode X3 for the left hand and the current electrode X4 for the right hand, and selects the voltage electrode Y2 for the right foot and the voltage electrode Y4 for the right hand. Thus, the electrode switching circuit 251 is controlled. The CPU 170 outputs current data Di indicating the magnitude of the reference current Iref flowing between the right hand and the left hand, and voltage data Dv indicating the potential difference between the right foot voltage electrode Y2 and the right hand voltage electrode Y4. From the above, the first bioelectric impedance ZaR on the upper right side of the trunk is measured. Here, the measured value of the first bioelectrical impedance at the nth (n ≧ 1) sampling timing is expressed as ZaR (n) ′.

  After step S20, the CPU 170 measures the second bioelectric impedance ZaL on the upper left side of the trunk. For example, the CPU 170 controls the electrode switching circuit 252 to select the current electrode X3 for the left hand and the current electrode X4 for the right hand, and selects the voltage electrode Y1 for the left foot and the voltage electrode Y3 for the left hand. Thus, the electrode switching circuit 251 is controlled. The CPU 170 outputs current data Di indicating the magnitude of the reference current Iref flowing between the right hand and the left hand, and voltage data Dv indicating the potential difference between the left foot voltage electrode Y1 and the left hand voltage electrode Y3. From the above, the second bioelectric impedance ZaL on the upper left side of the trunk is measured. Here, the measured value of the second bioelectric impedance at the nth (n ≧ 1) sampling timing is expressed as ZaL (n) ′.

  After step S30, the CPU 170 performs a smoothing process on each of the first bioelectrical impedance ZaR (n) ′ measured in step S20 and the second bioelectrical impedance ZaL (n) ′ measured in step S30 (step S30). S40). First, the smoothing process of the first bioelectrical impedance ZaR (n) ′ will be specifically described. The CPU 170 measures the measured value ZaR (n-2) ′ of the first bioelectrical impedance at the (n−2) th sampling timing and the measured value ZaR (n−) of the first bioelectrical impedance at the (n−1) th sampling timing. 1) ′ and a moving average process using the first bioelectrical impedance measured value ZaR (n) ′ at the nth sampling timing. And the process result is employ | adopted as a measured value of the 1st bioelectrical impedance in the nth sampling timing (smoothing process). Here, the measured value of the first bioelectrical impedance at the nth sampling timing after the smoothing process is performed is denoted as ZaR (n).

  Next, the smoothing process of the second bioelectrical impedance ZaL (n) ′ will be specifically described. The CPU 170 measures the measured value ZaL (n-2) ′ of the second bioelectrical impedance at the (n−2) th sampling timing and the measured value ZaL (n−) of the second bioelectrical impedance at the (n−1) th sampling timing. 1) ′ and a moving average process using the measured value ZaL (n) ′ of the second bioelectrical impedance at the n-th sampling timing. And the process result is employ | adopted as a measured value of the 2nd bioelectrical impedance in the nth sampling timing (smoothing process). Here, the measured value of the second bioelectrical impedance at the nth sampling timing after the smoothing process is performed is denoted as ZaL (n).

  After step S40, the CPU 170 executes a first centering process for generating a first centering value ZaR0 indicating the amplitude reference level of the measured value of the first bioelectrical impedance ZaR (step S50). Here, the first centering value at the nth sampling timing is expressed as ZaR0 (n). In the present embodiment, the CPU 170 starts the time point a predetermined time before the n-th sampling timing as the start point and the n-th sampling timing as the end point in each of the plurality of sampling timings in the centering period. Based on the measured value of the 1 bioelectrical impedance ZaR, the first centering value ZaR0 (n) at the nth sampling timing is generated. The time length of the centering period is variably set according to the breathing speed of the subject at the nth sampling timing. The specific contents will be described in detail below.

  FIG. 13 is a flowchart showing specific contents of the first centering process. As shown in FIG. 13, first, the CPU 170 executes an MA10 extraction process for extracting MA10 indicating the amplitude reference level of the measured value of the first bioelectrical impedance ZaR at each of the ten sampling timings (step S51). More specifically, the CPU 170 obtains the measured values (ZaR (n-9) to ZaR (n)) of the first bioelectric impedance ZaR at each of the n-9th to nth 10 sampling timings. The moving average processing is performed, and the processing result is extracted as MA10 (n) at the nth sampling timing ([Za (n−9) + Za (n−8) +... + Za (n)] / 10 → MA10 (n)).

  After step S51, the CPU 170 executes MA20 extraction processing for extracting MA20 indicating the amplitude reference level of the measurement value of the first bioelectrical impedance ZaR at each of the 20 sampling timings (step S52). More specifically, the CPU 170 obtains the measured values (ZaR (n-19) to ZaR (n)) of the first bioelectric impedance ZaR at each of the n-19th to nth 20 sampling timings. The moving average processing is performed, and the processing result is extracted as MA20 (n) at the nth sampling timing ([Za (n−19) + Za (n−18) +... + Za (n)] / 20 → MA20 (n)).

  After step S52, the CPU 170 executes MAX10 extraction processing for extracting the maximum value as MAX10 among the measured values of the first bioelectrical impedance ZaR at each of the ten sampling timings (step S53). More specifically, the CPU 170 calculates the maximum value among the measured values of the first bioelectrical impedance ZaR at each of the n-9th to nth sampling timings at the nth sampling timing. That is, it is extracted as MAX10 (n).

  After step S53, the CPU 170 executes a MIN10 extraction process for extracting the minimum value among the measured values of the first bioelectrical impedance ZaR at each of the ten sampling timings as MIN10 (step S54). More specifically, the CPU 170 obtains the minimum value among the measured values of the first bioelectrical impedance ZaR at each of the n-9th to nth sampling timings at the nth sampling timing. That is, it is extracted as MIN10 (n).

  After step S54, the CPU 170 performs a moving average process on the average value of MAX10 and MIN10 at each of the 20 sampling timings (the average value at the nth sampling timing is expressed as AV10 (n)). A median calculation process for calculating the result as a median is executed (step S55). More specifically, the CPU 170 performs a moving average process on average values (AV10 (n-19) to AV10 (n)) at each of the n-19th to nth 20 sampling timings, The processing result is extracted as the median value CNT20 (n) at the nth sampling timing ([AV10 (n−19) + AV10 (n−18) +... + AV10 (n)] / 20 → CNT20 (n) ). Although the description is omitted here, the median value CNT20 (n) is used to extract an abnormal waveform that is not suitable for processing due to artifacts (distortion of data waveform) caused by body movements or the like.

After step S55, the CPU 170 executes a breathing timing extraction process for extracting the breathing timing of the subject at the nth sampling timing (step S56). Hereinafter, specific contents of the breathing timing extraction process will be described with reference to FIGS. 14 and 15. 14 and 15 are flowcharts showing the specific contents of the breathing timing extraction process. As shown in FIG. 14, first, the CPU 170 executes a differential coefficient extraction process for extracting the differential coefficient dZaR (n) of the first bioelectrical impedance ZaR at the nth sampling timing (step S201). More specifically, the CPU 170 extracts the differential coefficient dZa (n) by executing arithmetic processing according to the following equation (3).
[ZaR (n) -ZaR (n-2)] / 1.2 = dZaR (n) (3)

  Next, the CPU 170 determines whether or not the absolute value of the differential coefficient dZaR (n) extracted in step S201 is smaller than 0.1 (step S202). If the result of step S202 is affirmative, the CPU 170 sets the polarity determination flag F0 (n) of the differential coefficient dZaR (n) to “0” and proceeds to step S204. The polarity determination flag F0 (n) being “0” means that the value of the first bioelectrical impedance ZaR is a maximum value (peak value) or a minimum value (bottom value) at the n-th sampling timing. means.

  On the other hand, when the result of step S202 is negative, the CPU 170 determines whether or not the value of the differential coefficient dZaR (n) is greater than 0 (step S203). If the result of step S203 is affirmative, the CPU 170 sets the polarity determination flag F0 (n) to “+1” and proceeds to step S204. The polarity determination flag F0 (n) being “+1” means that the direction of change of the first bioelectrical impedance ZaR is the positive side at the nth sampling timing. If the result of step S203 is negative, the CPU 170 sets the polarity determination flag F0 (n) to “−1” and proceeds to step S204. The polarity determination flag F0 (n) being “−1” means that the direction of change in the first bioelectrical impedance ZaR is negative at the nth sampling timing.

  In step S204, the CPU 170 makes the absolute value of the polarity determination flag F0 (n) at the nth sampling timing equal to the absolute value of the polarity determination flag F0 (n-1) at the (n-1) th sampling timing. In addition, it is determined whether the value of F0 (n-1) is not equal to the value of F0 (n). If the result of step S204 is affirmative, the CPU 170 sets F0 (n) to “0” and proceeds to the next step S206 (see FIG. 15). If the result of step S204 is negative, the CPU 170 proceeds to the next step S206 while maintaining the value of F0 (n) set immediately before step S204.

The description of the specific content of the breathing timing extraction process will be continued with reference to FIG. The CPU 170 determines whether or not the polarity determination flag F0 (n) at the nth sampling timing is “0” (step S206). If the result of step S206 is negative, the CPU 170 sets the peak / bottom determination flag F1 (n) to “0” and proceeds to step S209. The peak / bottom determination flag F1 (n) being “0” means that the measured value Za (n) of the first biopotential impedance at the nth sampling timing is not a peak value or a bottom value. .
On the other hand, when the result of step S206 is affirmative, the CPU 170 determines whether or not the sum of the polarity determination flags F0 at each of the three sampling timings is greater than “+1” (step S207). More specifically, the CPU 170 determines that the sum of the polarity determination flags (F0 (n-2) to F0 (n)) at each of the (n-2) th sampling timing to the nth sampling timing is "+1". It is judged whether it is larger than.

  If the result of step S207 is affirmative, the CPU 170 sets the peak / bottom determination flag F1 (n) to “+1”, and proceeds to step S209. The peak / bottom discrimination flag F1 (n) being “+1” means that the measured value ZaR (n) of the first bioelectrical impedance at the nth sampling timing is a peak value (maximum value). To do.

  If the result of step S207 is negative, the CPU 170 determines whether or not the sum of the polarity determination flags F0 at each of the three sampling timings is smaller than “−1” (step S208). More specifically, the CPU 170 determines that the sum of the polarity determination flags (F0 (n-2) to F0 (n)) at each of the (n-2) th sampling timing to the nth sampling timing is "-1". Or less.

  If the result of step S208 is affirmative, the CPU 170 sets the peak / bottom determination flag F1 (n) to “−1”, and proceeds to step S209. The peak / bottom discrimination flag F1 (n) being “−1” means that the measured value ZaR (n) of the first bioelectrical impedance at the nth sampling timing is a bottom value (minimum value). To do. On the other hand, if the result of step S208 is negative, the CPU 170 sets the peak / bottom discrimination flag F1 (n) to “0” and proceeds to step S209.

  In step S209, the CPU 170 determines whether or not the peak / bottom determination flag F1 (n) is “+1”. When the result of step S209 is negative, the CPU 170 adds 1 to the sampling counter value N (n−1) at the immediately preceding n−1th sampling timing (step S210), while the result of step S209 is positive. If so, the CPU 170 initializes the sampling counter value N (step S211). Here, as can be understood from FIGS. 9 and 10, a waveform showing a change in the first bioelectrical impedance ZaR accompanying respiration regardless of whether the subject breathing is chest breathing or abdominal breathing. Is substantially sinusoidal, the sampling counter value N is initialized (sampling counter value = 0) every time the measured value of the first bioelectrical impedance ZaR reaches the peak value, and until the next peak value is reached. The number of sampling timings is sequentially counted. Thus, the respiration timing extraction process in step S56 of FIG. 13 is completed.

  Returning to FIG. 13 again, the description will be continued. When the above-described respiration timing extraction process ends, the CPU 170 sets a respiration speed determination flag for determining whether the subject's respiration is fast or slow respiration (step S57). Hereinafter, specific contents of the breathing speed determination flag setting process executed by the CPU 170 in step S57 will be described with reference to FIG. FIG. 16 is a flowchart showing specific contents of the breathing speed determination flag setting process. As shown in FIG. 16, first, the CPU 170 determines whether or not the polarity determination flag F0 (n) is “0” (step S301). When the result of step S301 is negative, the CPU 170 determines that the breathing speed determination flag Fma (n) at the nth sampling timing is the breathing speed determination flag Fma (n−1) at the immediately preceding n−1th sampling timing. ) And the process ends.

  If the result of step S301 is affirmative, the CPU 170 determines whether or not the peak / bottom determination flag F1 (n) is “+1” (step S302). If the result of step S302 is affirmative, the CPU 170 determines whether or not the sampling counter value N (n−1) at the immediately preceding n−1th sampling timing is greater than “10” (step S303). . Here, if the subject's breathing speed is slow, the time length from when the measured value of the first bioelectrical impedance ZaR reaches the peak value until it reaches the next peak value becomes longer, and the next peak value is reached. The sampling counter value N immediately before reaching also increases. In the present embodiment, when the CPU 170 determines that the measured value of the first bioelectrical impedance ZaR has reached the peak value at the nth sampling timing, the sampling counter at the (n−1) th sampling timing immediately before that. It is determined whether or not the value is greater than “10”, and if it is determined that the sampling counter value is greater than “10”, it is determined that the subject's breathing is slow breathing. Specifically, if the result of step S303 is affirmative, the CPU 170 sets the breathing speed determination flag Fma (n) to “20” and ends the process. The breathing speed determination flag Fma (n) being “20” means that the subject's breathing is slow breathing. If the result of step S303 is negative, the CPU 170 determines that the subject's breathing is fast breathing, sets the breathing speed discrimination flag Fma (n) to “10”, and ends the process. The breathing speed determination flag Fma (n) being “10” means that the subject's breathing is fast breathing.

  On the other hand, when the result of step S302 is negative, the CPU 170 determines whether or not the peak / bottom determination flag F1 (n) is “−1” (step S304). When the result of step S304 is negative, the CPU 170 determines that the respiration speed determination flag Fma (n) at the nth sampling timing is the respiration speed determination flag Fma (n−1) at the immediately preceding n−1th sampling timing. ) And the process ends. If the result of step S304 is affirmative, the CPU 170 determines whether or not the sampling counter value N (n−1) at the immediately preceding (n−1) th sampling timing is greater than “5” (step S305). . In the present embodiment, when the sampling counter value N (n−1) immediately before reaching the bottom value is larger than “5”, the CPU 170 determines that the subject's breathing is slow breathing, while the bottom When the sampling counter value N (n−1) immediately before reaching the value is smaller than “5”, it is determined that the subject's breathing is fast breathing. Specifically, if the result of step S305 is affirmative, CPU 170 sets the respiration speed determination flag Fma (n) to “20” and ends the process, while the result of step S305 is negative. Indicates that the breathing speed determination flag Fma (n) is set to “10” and the process is terminated. Thus, the respiration speed determination flag setting process in step S57 of FIG. 13 is completed.

  Returning to FIG. 13 again, the description will be continued. When the above-described breathing speed determination flag setting process ends, the CPU 170 executes a first centering value extraction process for extracting the first centering value ZaR0 (n) (step S58). Hereinafter, specific contents of the first centering value extraction process executed by the CPU 170 in step S58 will be described with reference to FIG. FIG. 17 is a flowchart showing specific contents of the first centering value extraction process. As shown in FIG. 17, first, the CPU 170 determines whether or not the breathing speed determination flag Fma (n) is “10” (step S401). In other words, the CPU 170 determines whether or not the subject's breathing at the n-th sampling timing is fast breathing.

  In this embodiment, based on the measured value of the first bioelectrical impedance ZaR at each of a plurality of sampling timings within a centering period that is variably set according to the breathing rate of the subject, the first at the nth sampling timing. A centering value ZaR0 (n) is generated. If the result of step S401 is affirmative, that is, if the subject's breathing at the n-th sampling timing is a fast breath, the time length required for one fast breath (here, approximately 4.0 seconds) is centered. Set as period. That is, when the subject's breathing is fast breathing, a period from the n-9th sampling as the start point and the nth sampling timing as the end point is set as the centering period, and the n-9th to A first centering value ZaR0 (n) is generated based on the result of the moving average process using the measured value of the first bioelectrical impedance ZaR at each of the nth sampling timings. More specifically, when the result of step S401 is affirmative, the CPU 170 determines the first centering value ZaR0 (n) at the nth sampling timing based on MA10 (n) obtained in step S51 of FIG. Is generated (step S402). More specifically, the CPU 170 has a first centering value ZaR0 (n-2) at the (n-2) th sampling timing, a first centering value ZaR0 (n-1) at the (n-1) th sampling timing, The moving average processing is performed using MA10 (n), and the processing result is adopted as the first centering value ZaR0 (n) at the nth sampling timing ([ZaR0 (n−2) + ZaR0 (n−1). ) + MA10 (n)] / 3 → ZaR0 (n)).

  On the other hand, if the result of step S401 is negative, that is, if the subject's breathing at the n-th sampling timing is a slow breath, the length of time required for that slow breath (here, approximately 8.0) Second) is set as the centering period. That is, when the subject's breathing is slow breathing, the period from the n-19th sampling as the start point and the nth sampling timing as the end point is set as the centering period. A first centering value ZaR0 (n) is generated based on the result of the moving average process using the measured value of the first bioelectrical impedance ZaR at each of the nth sampling timings. More specifically, when the result of step S401 is negative, the CPU 170 determines the first centering value ZaR0 (n) at the nth sampling timing based on the MA 20 (n) obtained in step S52 of FIG. Is generated (step S403). More specifically, the CPU 170 performs moving average processing using ZaR0 (n-2), ZaR0 (n-1), and MA20 (n), and the processing result is obtained at the nth sampling timing. The first centering value ZaR0 (n) is adopted ([ZaR0 (n-2) + ZaR0 (n-1) + MA20 (n)] / 3 → ZaR0 (n)). Thus, the first centering process in step S50 of FIG. 12 is completed.

  As described above, the waveform indicating the change in the bioelectrical impedance Za of the upper trunk is substantially sinusoidal regardless of whether the subject's breathing is chest breathing or abdominal breathing. The waveform indicating the change in the first bioelectrical impedance ZaR is also substantially sinusoidal. Even if the waveform indicating the change in the first bioelectrical impedance ZaR is disturbed (even if an artifact occurs) due to the influence of body movement or the like, the CPU 170 has a predetermined number so that the first centering value ZaR0 corresponding to the waveform is obtained. The first centering value ZaR0 is generated based on the measured value of the first bioelectrical impedance ZaR at each of the sampling timings. More specifically, for each sampling timing, the CPU 170 starts at a time point that is a predetermined time length before the sampling timing and starts at the sampling timing in each of a plurality of sampling timings within the centering period with the sampling timing as an end point. 1 The moving average process using the measured value of the bioelectrical impedance ZaR is performed, and based on the result, the first centering value ZaR0 at the sampling timing is obtained. Therefore, the first bioelectrical impedance ZaR is affected by the body movement. Even if the waveform indicating the change is disturbed, the first centering value ZaR0 corresponding to the waveform can be generated with high accuracy. The time length of the centering period corresponding to each sampling timing is variably set according to the breathing rate of the subject at the sampling timing.

  As shown in FIG. 12, after step S50, the CPU 170 executes a second centering process for generating a second centering value ZaL0 indicating the amplitude reference level of the measured value of the second bioelectrical impedance ZaL (step S60). Here, the second centering value at the nth sampling timing is expressed as ZaL0 (n). Similar to the first centering value ZaR0 (n) described above, the CPU 170 has a centering period in which the start point is a predetermined time length before the nth sampling timing and the end point is the nth sampling timing. The second centering value ZaL0 (n) at the nth sampling timing is generated based on the measured value of the second bioelectrical impedance ZaL at each of the plurality of sampling timings. The specific content of the method for generating the second centering value ZaL0 (n) is the same as the method for generating the first centering value ZaR0 (n), and thus detailed description thereof is omitted.

  As shown in FIG. 12, when the second centering process in step S60 is completed, the CPU 170 performs a first relative value that is a relative value of the first bioelectrical impedance measured value ZaR (n) with respect to the first centering value ZaR0 (n). A first relative value calculation process for calculating the value ΔZaR (n) is executed (step S70). More specifically, the CPU 170 obtains a difference between the first bioelectric impedance ZaR (n) obtained in step S40 and the first centering value ZaR0 (n) obtained in step S50, and the obtained difference value is obtained. The first relative value ΔZaR (n) at the nth sampling timing is employed.

  After step S70, the CPU 170 calculates a second relative value ΔZaL (n) that is a relative value of the second bioelectrical impedance measurement value ZaL (n) with respect to the second centering value ZaL0 (n). Processing is executed (step S80). More specifically, the CPU 170 obtains a difference between the second bioelectrical impedance ZaL (n) obtained in step S40 and the second centering value ZaL0 (n) obtained in step S60, and uses the obtained difference value. The second relative value ΔZaL (n) at the nth sampling timing is employed.

  For example, when the subject is a healthy person, there is no functional difference (difference in ventilation capacity) between the right lung and the left lung. Therefore, as shown in FIG. 18, the first relative value ΔZaR associated with the subject's breathing. The waveform indicating the change with time of the waveform and the waveform indicating the change with time of the second relative value ΔZaL are substantially similar. The waveform indicating the temporal change of the first relative value ΔZaR is based on the first centering value ZaR0, which is the amplitude reference level of the measured value of the first bioelectrical impedance ZaR, as the zero reference. The waveform indicating the change in the state is based on the second centering value ZaL0, which is the amplitude reference level of the measured value of the second bioelectrical impedance ZaL, as a zero reference. As shown in FIG. 18, in the inspiration, the first relative value ΔZaR and the second relative value ΔZaL are positive values, whereas in the expiration, the first relative value ΔZaR and the second relative value ΔZaL are negative values. The amplitude value of the first relative value ΔZaR increases as the amount of ventilation in the right lung increases. Furthermore, the absolute value of the peak value (maximum positive value) of the first relative value ΔZaR increases as the amount of inhalation in the right lung increases, and the bottom value increases as the amount of expiration in the right lung increases. The absolute value of (the minimum negative value) is a large value. Similarly, the greater the left lung ventilation, the greater the amplitude value of the second relative value ΔZaL. The absolute value of the peak value of the second relative value ΔZaL becomes larger as the amount of inhalation in the left lung increases, and the absolute value of the bottom value becomes larger as the amount of expiration in the left lung increases.

  As shown in FIG. 12, after step S80, the CPU 170 executes a first right lung respiration level extraction process for extracting a first right lung respiration level BR1 indicating the ventilation ability of the upper part of the right lung (step S90). ). Hereinafter, specific contents of the first right lung respiration level extraction process executed by the CPU 170 in step S90 will be described with reference to FIG. FIG. 19 is a flowchart showing specific contents of the first right lung respiration level extraction process. As shown in FIG. 19, first, the CPU 170 determines whether or not the subject's breathing is inspiration (step S501). Specifically, the CPU 170 determines that the intake is in the case where the value of the first relative value ΔZaR (n) at the n-th sampling timing is a positive value, whereas the CPU 170 determines that it is a negative value. For example, it is determined that the breath is expired. If the CPU 170 determines that it is inspiration, it sets the inspiration determination flag F2 to “+1”, while if it determines that it is expiration, it sets the inspiration determination flag F2 to “0”. In the initial state, the intake determination flag F2 is set to “+1”. In step S501, the CPU 170 may determine whether the intake is based on the second relative value ΔZaL (n) instead of the first relative value ΔZaR (n).

  If the result of step S501 is affirmative, the CPU 170 executes peak hold processing (step S502). More specifically, the CPU 170 holds the maximum value among the first relative values ΔZaR at each of a plurality of sampling timings during intake as the peak value ΔZaR (MAX). On the other hand, if the result of step S501 is negative, the CPU 170 executes a bottom hold process (step S503). More specifically, the CPU 170 holds the minimum value among the first relative values ΔZaR at each of a plurality of sampling timings during expiration as the bottom value ΔZaR (MIN).

  Next, the CPU 170 determines whether or not the nth sampling timing is the first zero cross timing at which the first bioelectrical impedance measurement value ZaR (n) and the first centering value ZaR0 (n) are equal. Determination is made (step S504). More specifically, the CPU 170 executes a first zero cross timing determination process, and determines whether the sampling timing is the first zero cross timing based on the processing result. The detailed contents will be described below.

  FIG. 20 is a flowchart showing specific contents of the first zero cross timing determination process executed by the CPU 170 in step S504. As shown in FIG. 20, first, the CPU 170 extracts the minimum value from the first relative values ΔZaR at each of the five sampling timings (step S601). More specifically, the CPU 170 determines the absolute value | ΔZaR | (| ΔZaR (n−4) | to | ΔZaR (n) of the first relative value ΔZaR at each of the n−4th to n-th sampling timings. |) Is extracted as the first cross-point determination value ΔMIN5 (n) at the n-th sampling timing.

  After step S60, the CPU 170 determines whether the first cross point determination value at the previous sampling timing is equal to the first cross point determination value extracted at step S601, and whether the previous sampling timing is the first zero cross timing. It is determined whether or not (step S602). More specifically, the CPU 170 determines that the first cross-point determination values ΔMIN5 (n−1) and ΔMIN5 (n) at the (n−1) th sampling timing are equal, and at the (n−1) th sampling timing. It is determined whether or not the first cross point determination flag F3 (n−1) is set to “+1”. When the first cross point determination flag F3 (n−1) is set to “+1”, the (n−1) th sampling timing is regarded as the first zero cross timing. The initial value (default value) of the first cross point determination flag F3, that is, the value of the first cross point determination flag F3 (1) at the first sampling timing is set to “0”.

  If the result of step S602 is positive, the CPU 170 determines that the nth sampling timing is not the first zero cross timing, sets the first crosspoint determination flag F3 (n) to “0”, and then proceeds to step S74. move on. If the result of step S602 is negative, the CPU 170 determines whether or not the absolute value of the first relative value ΔZaR (n) at the nth sampling timing is 0.3 or less (step S603). If the result of step S603 is negative, the CPU 170 determines that the nth sampling timing is not the first zero cross timing, sets the first cross point determination flag F3 (n) to “0”, and ends the process. To do. If the result of step S603 is affirmative, the CPU 170 determines that the nth sampling timing is the first zero cross timing, sets the first crosspoint determination flag F3 (n) to “+1”, and performs processing. finish. Thus, the first zero cross timing determination process is completed.

  Returning to FIG. 19 again, the description will be continued. If the CPU 170 determines in step S504 that the nth sampling timing is not the first cross timing, that is, if the first cross point determination flag F3 (n) is “0”, the sampling timing is determined. The first right lung respiration level extraction process at ends. On the other hand, if the CPU 170 determines that the nth sampling timing is the first zero cross timing, that is, if the first crosspoint determination flag F3 (n) is “+1”, the process proceeds to step S505.

  In step S505, the CPU 170 determines whether or not the differential coefficient dZaR of the first bioelectrical impedance ZaR at the nth sampling timing is positive (> 0). In other words, the CPU 170 determines whether or not the nth sampling timing is a timing at which the exhalation changes to inspiration.

  When the result of step S505 is affirmative, the CPU 170 determines that the nth sampling timing is a timing at which the expiration changes from inspiration to inspiration, and the peak value ΔZaR (MAX) and the bottom value held at that time are determined. The sum of absolute values with ΔZaR (MIN) is extracted as the first right lung respiration level BR1 in the immediately preceding one breath (step S506). The first right lung respiration level BR1 extracted in step S506 indicates the ventilation capacity of the upper part of the right lung in the last one breath. The higher the ventilation capacity, the first right lung respiration level BR1. It shows a large value. Thereafter, the CPU 170 executes an intake flag setting process (step S507). More specifically, the CPU 170 sets the intake determination flag F2 to “+1”. Then, the CPU 170 initializes the peak hold process (step S508). More specifically, the CPU 170 sets (initializes) the peak value ΔZaR (MAX) held in step S502 to “0”, and performs the first right lung respiration level extraction process at the sampling timing. finish.

  On the other hand, if the result of step S505 is negative, the CPU 170 determines that the n-th sampling timing is a timing at which the change from inspiration to expiration is performed, and executes an expiration flag setting process (step S509). More specifically, the CPU 170 sets the intake determination flag F2 to “0”. Then, the CPU 170 initializes bottom hold processing (step S510). More specifically, the CPU 170 sets (initializes) the bottom value ΔZaR (MIN) held in step S503 to “0”, and ends the first right lung level extraction process at the sampling timing. To do. Thus, the first right lung respiration level extraction process in step S90 of FIG. 12 is completed.

  As shown in FIG. 12, after step S90, the CPU 170 executes a first left lung respiration level extraction process for extracting a first left lung respiration level BL1 indicating the ventilation capacity of the upper part of the left lung (step S100). ). The specific contents of the first left lung respiration level extraction process are the same as those of the first right lung respiration level extraction process described above, and a detailed description thereof will be omitted. In short, the nth sampling timing is the second zero cross timing at which the measured value ZaL (n) of the second bioelectrical impedance is equal to the second centering value ZaL0 (n), and from inspiration to expiration. If it is determined that the timing changes, the sum of absolute values of the peak value ΔZaL (MAX) and the bottom value ΔZaL (MIN) held at that time is the first left lung respiration in the immediately preceding one respiration. It is extracted as level BL1. The first left lung respiration level BL1 thus extracted indicates the ventilation capacity of the upper part of the left lung in the last one breath, and the higher the ventilation capacity, the first left lung respiration level BL1. Indicates a large value.

<A-5: Respiration level display process>
Next, a respiration level display process executed by the CPU 170 will be described. In the present embodiment, the CPU 170 executes a breathing level display process for displaying the first right lung breathing level BR1 and the first left lung breathing level BL1 in one breath for each breath of the subject. As shown in FIG. 21, for each breath of the subject, the CPU 170 displays the first right lung breathing level BR1 in the one breath with the first bar graph BG1, and the first left lung breathing in the one breath. The display unit 160 is controlled to display the level BL1 as the second bar graph BG2. More specifically, the CPU 170 determines the number of steps of the first bar graph BG1 to be colored and displayed according to the first right lung respiration level BR1 in one respiration immediately before the respiration level detection process. At the same time, the number of stages of the second bar graph BG2 to be colored and displayed is determined according to the respiratory level BL1 of the first left lung in one breath immediately before the respiratory level detection process described above. Then, the CPU 170 determines the number of stages of the first bar graph BG1 to be colored and displayed in accordance with each of the peak value ΔZaR (MAX) and the bottom value ΔZaR (MIN) constituting the first right lung respiration level BR1. The second bar graph BG2 to be colored and displayed according to each of the peak value ΔZaL (MAX) and the bottom value ΔZaL (MIN) constituting the first left lung respiration level BL1 while allocating to inspiration and expiration Allocate stages to inspiration and expiration.

  Furthermore, as the peak value ΔZaR (MAX) constituting the first right lung respiration level BR1 increases, the number of steps on the inhalation side of the first bar graph BG1 increases, and the value of the bottom value ΔZaR (MIN) increases. The larger the is, the greater the number of stages on the expiration side of the first bar graph BG1. Similarly, the larger the peak value ΔZaL (MAX) constituting the first left lung respiration level BL1, the greater the number of steps on the inhalation side of the second bar graph BG2, and the bottom value ΔZaL (MIN) becomes smaller. The larger the number, the greater the number of steps on the exhalation side of the second bar graph BG2.

  As described above, in this embodiment, the CPU 170 controls to display the first right lung respiration level BR1 and the first left lung respiration level BL1 in one respiration for each respiration of the subject. Therefore, the subject can easily recognize the difference between the ventilation ability of his / her right lung and the ventilation ability of the left lung. If the test subject is healthy, there is no functional difference between the right and left lungs, so the number of steps displayed in the first bar graph BG1 and the number of steps displayed in the second bar graph BG2 There is no difference between the two. On the other hand, if the subject has a disease in one of the left and right lungs, a functional difference occurs between the right lung and the left lung, so the first right lung respiratory level BR1 and the first lung A difference arises from the left lung respiration level BL1. That is, there is a difference between the number of steps displayed on the first bar graph BG1 and the number of steps displayed on the second bar graph BG2. Subjects can easily recognize the difference between their right lung ventilation ability and left lung ventilation ability by looking at the first bar graph BG1 and the second bar graph BG2, so it is easy to identify the diseased part Can do. Moreover, the display by 1st bar graph BG1 and 2nd bar graph BG2 can also be utilized as biofeedback information for the function recovery of the lungs after surgery, for example.

<B: Second Embodiment>
Next, a second embodiment of the present invention will be described. Since the configuration and operation of the biometric apparatus according to the second embodiment are substantially the same as those of the first embodiment described above, the description of the overlapping parts is omitted. In the present embodiment, for each breath of the subject, the CPU 170 performs not only the first right lung breathing level BR1 and the first left lung breathing level BL1, but also the second right that indicates the ventilation ability of the middle lower part of the right lung. It is different from the first embodiment described above in that control is performed so that the pulmonary respiratory level BR2 and the second left pulmonary respiratory level BL2 indicating the ventilation capability of the middle and lower part of the left lung are displayed. Hereinafter, specific contents will be described.

  The bioelectrical impedance Zb of the middle trunk includes the bioelectrical impedance on the right side of the middle trunk including the middle lower part and the abdomen of the right lung, and the bioelectrical impedance on the left side of the middle trunk including the middle lower part of the left lung and the abdomen. Is included. Hereinafter, in the present specification, the bioelectrical impedance on the right side of the middle trunk is denoted as third bioelectrical impedance ZbR, and the bioelectrical impedance on the left side of the middle trunk is denoted as fourth bioelectrical impedance ZbL. The third bioelectrical impedance ZbR is obtained from current data Di indicating the magnitude of the reference current Iref flowing between the right hand and the right foot, and voltage data Dv indicating the potential difference between the left hand and the left foot. Further, the fourth bioelectrical impedance ZbL is obtained from the current data Di indicating the magnitude of the reference current Iref flowing between the left hand and the left foot and the voltage data Dv indicating the potential difference between the right hand and the right foot. It is.

  The third bioelectrical impedance ZbR also changes as air enters and exits the right lung with breathing. The change is similar to the bioelectrical impedance Zb in the middle trunk described above, but the larger the right lung ventilation, the larger the amplitude value of the third bioelectrical impedance ZbR. In the present embodiment, focusing on the fact that the amplitude value of the third bioelectrical impedance ZbR is a value corresponding to the ventilation ability of the middle and lower part of the right lung, based on the measured value of the third bioelectrical impedance ZbR, the right lung The second right lung respiration level BR2 indicating the middle and lower ventilation capacity is obtained. Details of this will be described later.

  In addition, the fourth bioelectrical impedance ZbL also changes as air enters and leaves the left lung with breathing. The method of the change is the same as the bioelectrical impedance Zb of the middle trunk described above, but the amplitude value of the fourth bioelectrical impedance ZbL increases as the ventilation volume of the left lung increases. In the present embodiment, focusing on the fact that the amplitude value of the fourth bioelectrical impedance ZbL is a value corresponding to the ventilation capacity of the middle and lower part of the left lung, based on the measured value of the fourth bioelectrical impedance ZbL, The second left lung respiration level BL2 indicating the middle and lower ventilation capacity is obtained. Details of this will be described later.

  Next, the specific content of the respiration level detection process in this embodiment is demonstrated. 22 and 23 are flowcharts for explaining the specific contents of the respiration level detection process in the present embodiment. As shown in FIG. 22, first, the CPU 170 determines whether or not the sampling timing has been reached (step S700), and proceeds to step S710 if the result of step S700 is affirmative. Here, assuming the case where the nth sampling timing has been reached, the specific contents of each step after step S710 will be described. In addition, about the part which overlaps with 1st Embodiment, description is abbreviate | omitted suitably.

  As shown in FIG. 22, in step S710, the CPU 170 measures the first bioelectric impedance ZaR on the upper right side of the trunk. Since this content is the same as that of the first embodiment, a detailed description is omitted. Next, the CPU 170 measures the third bioelectric impedance ZbR on the right side of the middle trunk (step S720). For example, the CPU 170 controls the electrode switching circuit 252 so as to select the current electrode X2 for the right foot and the current electrode X4 for the right hand, and selects the voltage electrode Y1 for the left foot and the voltage electrode Y3 for the left hand. Thus, the electrode switching circuit 251 is controlled. The CPU 170 outputs current data Di indicating the magnitude of the reference current Iref flowing between the right hand and the right foot, and voltage data Dv indicating the potential difference between the left foot voltage electrode Y1 and the left hand voltage electrode Y3. From this, the third bioelectrical impedance ZbR on the right side of the trunk is measured. Here, the measured value of the third bioelectrical impedance at the nth sampling timing is denoted as ZbR (n) '.

  After step S720, the CPU 170 performs a smoothing process on each of the first bioelectric impedance ZaR (n) ′ obtained in step S710 and the third bioelectric impedance ZbR (n) ′ obtained in step S720 (step S720). S730). Since the content of the smoothing process is the same as that of the first embodiment, detailed description thereof is omitted. The measured value of the third bioelectrical impedance at the nth sampling timing after the smoothing process is performed is denoted as ZbR (n).

  After step S730, the CPU 170 measures the second bioelectric impedance ZaL on the upper left side of the trunk (step S740). Since this content is the same as that of the first embodiment, a detailed description is omitted. Next, the CPU 170 measures the fourth bioelectrical impedance ZbL on the left side of the middle trunk (step S750). For example, the CPU 170 controls the electrode switching circuit 252 so as to select the current electrode X1 for the left foot and the current electrode X3 for the left hand, and selects the voltage electrode Y2 for the right foot and the voltage electrode Y4 for the right hand. Thus, the electrode switching circuit 251 is controlled. The CPU 170 outputs current data Di indicating the magnitude of the reference current Iref flowing between the left hand and the left foot, and voltage data Dv indicating the potential difference between the right foot voltage electrode Y2 and the right hand voltage electrode Y4. Then, the fourth bioelectrical impedance ZbL on the left side of the trunk is measured. Here, the measured value of the fourth bioelectrical impedance at the nth sampling timing is denoted as ZbL (n) '.

  After step S750, the CPU 170 performs a smoothing process on each of the second bioelectric impedance ZaL (n) ′ obtained in step S740 and the fourth bioelectric impedance ZbL (n) ′ obtained in step S750 (step S750). S760). Since the content of the smoothing process is the same as that of the first embodiment, detailed description thereof is omitted. The measured value of the fourth bioelectrical impedance at the nth sampling timing after the smoothing process is performed is denoted as ZbL (n).

  As shown in FIG. 22, in step S770 after step S760, the CPU 170 executes a first centering process. In step S780 after step S770, the CPU 170 executes a first relative value calculation process. In step S790 after step S780, the CPU 170 executes a first right lung respiration level extraction process. Since the processing in each of the above steps S770 to S790 is the same as the content described in the first embodiment, detailed description is omitted.

  After step S790, the CPU 170 generates a third centering value ZbR0 indicating the amplitude reference level of the measurement value of the third bioelectrical impedance ZbR, and uses the generated third centering value ZbR0 to generate the third bioelectrical impedance ZbR. A third relative value ΔZbR that is a relative value of the measured value of the measured value to the third centering value ZbR0 is calculated (step S800). The third centering value ZbR0 indicates an amplitude reference level for extracting information resulting from respiration from a waveform indicating a temporal change in the third bioelectrical impedance ZbR.

  Here, as described above, when the subject's breathing is abdominal breathing, the change in the bioelectric impedance Zb in the middle trunk is different from the change in the bioelectric impedance Za in the upper trunk (non-sinusoidal). Thus, similar to the case of obtaining the first centering value ZaR0 or the second centering value ZaL0, the moving average process using the measured value of the third bioelectrical impedance ZbR at each of a predetermined number of sampling timings may be performed. Thus, it is difficult to accurately obtain the amplitude reference level for extracting information resulting from respiration from these amplitude reference levels, that is, from the waveform indicating the temporal change of the third bioelectrical impedance ZbR.

  Therefore, in the present embodiment, as shown in FIG. 24, a first zero cross timing at which the measured value of the first bioelectrical impedance ZaR and the first centering value ZaR0 are equal is extracted, and the third zero cross timing at the first zero cross timing is extracted. A third centering value ZbR0 is generated based on the measured value of the bioelectrical impedance ZbR. Thereby, even if the subject's breathing is abdominal breathing, the amplitude reference level of the measured value of the third bioelectrical impedance ZbR can be extracted with high accuracy. FIG. 24 is a diagram for conceptually explaining a method of generating the third centering value ZbR0. Hereinafter, specific contents of the third relative value calculation process executed by the CPU 170 in step S800 will be described with reference to FIG.

  FIG. 25 is a flowchart showing specific contents of the third relative value calculation process. As shown in FIG. 25, first, the CPU 170 determines whether or not the first cross point determination flag F3 (n) described above is “+1” (step S801). If the result of step S801 is affirmative, that is, if the nth sampling timing is the first zero-crossing timing, the CPU 170 extracts the third centering value ZbR0 (n) (step S802). More specifically, the CPU 170 extracts the measured value ZbR (n) of the third bioelectrical impedance at the nth sampling timing as the third centering value ZbR0 (n). More specifically, the CPU 170 has a third centering value ZbR0 (n-2) at the (n-2) th sampling timing, a third centering value ZbR0 (n-1) at the (n-1) th sampling timing, The moving average process is performed using the third centering value ZbR0 (n) at the nth sampling timing, and the processing result is extracted as the third centering value ZbR0 (n) at the nth sampling timing ([[ ZbR0 (n-2) + ZbR0 (n-1) + ZbR0 (n)] / 3-> ZbR0 (n)).

  On the other hand, if the result of step S801 is negative, that is, if the nth sampling timing is not the first zero cross timing, the CPU 170 determines the third centering value ZbR0 (n at the immediately preceding (n-1) th sampling timing. −1) is adopted as the third centering value ZbR0 (n) at the nth sampling timing (ZbR0 (n−1) → ZbR0 (n)).

  Next, the CPU 170 calculates a third relative value ΔZbR (n) at the nth sampling timing (step S804). More specifically, the CPU 170 calculates the difference between the measured value ZbR (n) of the third bioelectrical impedance and the third centering value ZbR0 (n) as the third relative value ΔZbR (n at the nth sampling timing. ) Is adopted. Thus, the third relative value calculation process in step S800 of FIG. 22 ends.

  Returning to FIG. 22 again, the description will be continued. As shown in FIG. 22, after step S800, the CPU 170 executes a second right lung respiration level extraction process for extracting a second right lung respiration level BR2 indicating the ventilation capability of the middle lower part of the right lung (step S800). S810). Hereinafter, the specific contents of the second right lung respiration level extraction process executed by the CPU 170 in step S810 will be described with reference to FIG. FIG. 26 is a flowchart showing specific contents of the second right lung respiration level extraction process. As shown in FIG. 26, first, the CPU 170 determines whether or not the subject's breathing is inspiration (step S900). Since this content is the same as the content described in the first right lung respiration level extraction process (step S501 in FIG. 19), detailed description is omitted.

  If the result of step S900 is affirmative, the CPU 170 executes peak hold processing (step S901). More specifically, the CPU 170 holds the maximum value as the peak value ΔZbR (MAX) among the third relative values ΔZbR at each of a plurality of sampling timings during intake. On the other hand, if the result of step S900 is negative, the CPU 170 executes a bottom hold process (step S902). More specifically, the CPU 170 holds the minimum value among the third relative values ΔZbR at each of a plurality of sampling timings during expiration as the bottom value ΔZbR (MIN).

  Next, the CPU 170 determines whether or not the first cross point determination flag F3 (n) described above is “+1” (step S903). If the result of step S903 is negative, that is, if the nth sampling timing is not the first zero cross timing, the second right lung respiratory level extraction process at the sampling timing ends. On the other hand, if the result of step S903 is positive, that is, if the nth sampling timing is the first zero-crossing timing, the process proceeds to step S904. In step S904, the CPU 170 determines whether or not the differential coefficient dZaR of the first bioelectrical impedance ZaR at the nth sampling timing is positive (> 0), as in step S505 of FIG. In other words, the CPU 170 determines whether or not the nth sampling timing is a timing at which the exhalation changes to inspiration.

  If the result of step S904 is affirmative, the CPU 170 determines that the nth sampling timing is a timing at which the expiration changes from expiration to inspiration, and the peak value ΔZbR (MAX) and the bottom value held at that time are determined. The sum of absolute values with ΔZbR (MIN) is extracted as the second right lung respiration level BR2 in the last one respiration (step S905). The second right lung respiration level BR2 extracted in step S905 indicates the ventilation ability of the middle and lower parts of the right lung in the one breath. The higher the ventilation ability, the more the second right lung respiration level BR2 is. It shows a large value. Thereafter, the CPU 170 executes an intake flag setting process (step S906). More specifically, the CPU 170 sets the intake determination flag F2 to “+1”. Then, the CPU 170 initializes the peak hold process (step S907). More specifically, the CPU 170 sets (initializes) the peak value ΔZbR (MAX) held in step S812 to “0”, and performs the second right lung respiratory level extraction process at the sampling timing. finish.

  On the other hand, when the result of step S904 is negative, the CPU 170 determines that the n-th sampling timing is a timing when the inspiration changes to the expiration, and executes the expiration flag setting process (step S908). More specifically, the CPU 170 sets the intake determination flag F2 to “0”. Then, the CPU 170 initializes the bottom hold process (step S909). More specifically, the CPU 170 sets (initializes) the bottom value ΔZbR (MIN) held in step S813 to “0”, and ends the first right lung level extraction process at the sampling timing. To do. Thus, the second right lung respiration level extraction process in step S810 of FIG. 22 ends, and the process proceeds to the next step S820 (see FIG. 23).

  With reference to FIG. 23, the description of the specific content of the respiration level detection process will be continued. As shown in FIG. 23, in step S820, the CPU 170 executes a second centering process. In step S830 after step S820, the CPU 170 executes a second relative value calculation process. In step S840 after step S830, CPU 170 executes a first left lung respiration level extraction process. Since the processing in each of the above steps S820 to S840 is the same as the content described in the first embodiment, detailed description thereof is omitted.

  After step S840, the CPU 170 generates a fourth centering value ZbL0 indicating the amplitude reference level of the measurement value of the fourth bioelectrical impedance ZbL, and uses the generated fourth centering value ZbL0 to generate the fourth bioelectrical impedance ZbL. A fourth relative value ΔZbL that is a relative value of the measured value to the fourth centering value ZbL0 is calculated (step S850). The fourth centering value ZbL0 indicates an amplitude reference level for extracting information resulting from respiration from a waveform indicating a temporal change in the fourth bioelectrical impedance ZbL. In the present embodiment, the second zero cross timing at which the measured value of the second bioelectric impedance ZaL and the second centering value ZaL0 are equal is extracted, and based on the measured value of the fourth bioelectric impedance ZbL at the second zero cross timing. To generate the fourth centering value ZbL0. The specific content of the method for generating the fourth centering value ZbL0 (n) at the nth sampling timing is the same as the method for generating the third centering value ZbR0 (n) described above. Omitted. The CPU 170 employs the difference between the fourth bioelectrical impedance measurement value ZbL (n) and the fourth centering value ZbL0 (n) as the fourth relative value ΔZbL (n) at the nth sampling timing. .

As shown in FIG. 23, after step S850, the CPU 170 executes a second left lung respiratory level extraction process for extracting a second left lung respiratory level BL2 indicating the ventilation capability of the middle lower part of the left lung (step S850). S860).
Since the specific content of the second left lung respiration level extraction process is the same as that of the second right lung respiration level extraction process, detailed description thereof is omitted. In short, the nth sampling timing is the second zero cross timing at which the measured value ZaL (n) of the second bioelectrical impedance is equal to the second centering value ZaL0 (n), and from expiration to inspiration. If it is determined that the timing changes, the sum of absolute values of the peak value ΔZbL (MAX) and the bottom value ΔZbL (MIN) held at that time is the second left lung respiration in the immediately preceding one breath It is extracted as level BL2. The second left lung respiration level BL2 extracted in this way indicates the ventilation ability of the middle lower part of the left lung in the one breath. The higher the ventilation ability, the second left lung respiration level BL2 Indicates a large value. This completes the respiration level detection process at the nth sampling timing.

  Next, a respiration level display process executed by the CPU 170 will be described. In the present embodiment, the CPU 170 performs the second right lung respiration in the one breath in addition to the first right lung respiration level BR1 and the first left lung respiration level BL1 in the one breath for each breath of the subject. A breathing level display process for displaying the level BR2 and the second left lung breathing level BL2 is executed. As shown in FIG. 27, the CPU 170 displays the first right lung respiration level BR1 as the first bar graph BG1 and the first left lung respiration level BL1 as the second bar graph BG2 for each breath of the subject. The display unit 160 is controlled so that the second right lung respiration level BR2 is displayed as a third barruff BG3 and the second left lung respiration level BL2 is displayed as a fourth bar graph BG4. Since the display mode by the first bar graph BG1 and the second bar graph BG2 is the same as that of the first embodiment, detailed description thereof is omitted. Hereinafter, a display mode using the third bar graph BG3 and the fourth bar graph BG4 will be described.

  The CPU 170 determines the number of steps of the third bar graph BG3 to be colored and displayed in accordance with the second right lung respiration level BR2 in one respiration immediately before detected in the respiration level detection process, and the respiration described above. The number of stages of the fourth bar graph BG4 to be colored and displayed is determined in accordance with the second left lung respiration level BL2 in the last one respiration detected by the level detection process. Then, the CPU 170 determines the number of steps of the third bar graph BG3 to be colored and displayed in accordance with each of the peak value ΔZbR (MAX) and the bottom value ΔZbR (MIN) constituting the second right lung respiration level BR2. The fourth bar graph BG4 to be colored and displayed according to each of the peak value ΔZbL (MAX) and the bottom value ΔZbL (MIN) constituting the second left lung respiration level BL2 while allocating to inspiration and expiration The number of stages is assigned to inspiration and expiration.

  As described above, in this embodiment, the CPU 170 performs the first right lung respiration level BR1, the second right lung respiration level BR2, and the first left lung respiration for each respiration of the subject. Controls to display level BL1 and the second left lung breathing level BL2, so that the subject not only has the ability to ventilate the upper right lung and the upper left lung, but also in the right lung. The lower ventilation capacity and the middle lower ventilation capacity of the left lung can also be easily recognized. In other words, by looking at the first bar graph BG1 to the fourth bar graph BG4, the subject not only shows the difference between the ventilation capacity of the upper part of his right lung and the ventilation capacity of the upper part of the left lung, but also the middle lower part of the right lung. The difference between the ventilation capacity of the left lung and the ventilation capacity of the middle lower part of the left lung can be easily recognized.

  In the second embodiment described above, in addition to the first right lung respiratory level BR1 and the first left lung respiratory level BL1, the second right lung respiratory level BR2 and the second left lung respiratory level BL2 are measured. However, the present invention is not limited to this. For example, the first right lung respiratory level BR1 and the first left lung respiratory level BL1 are not measured, and the second right lung respiratory level BR2 and the second left lung respiratory level are not measured. There may be a mode in which BL2 is measured. However, in this aspect (an aspect in which the right lung respiration level and the left lung respiration level are measured based only on the measured values of the third bioelectric impedance ZbR and the fourth bioelectric impedance ZbL), the third bioelectricity associated with the respiration of the subject is used. Since the waveform showing the change over time of the impedance ZbR and the fourth bioelectrical impedance ZbL includes waveform distortion caused by abdominal breathing during expiration, the waveform distortion during expiration is determined by discriminating between expiration and inspiration. It is also possible to use the exhaled breath information as respiratory level information. A method for discriminating expiration and inspiration is arbitrary. For example, it is possible to discriminate expiration and inspiration using respiration assist information for instructing a respiration method. Even if breathing assist information is not used, if there is no waveform distortion during expiration due to abdominal breathing, waveform distortion is extracted assuming a sine wave, and expiration and inspiration are determined based on the magnitude of the waveform distortion. Can also be determined.

<C: Third Embodiment>
Next, a third embodiment of the present invention will be described. In the third embodiment, the CPU 170 performs a right lung respiration level (first right lung respiration level BR1, second right lung respiration level BR2) indicating the ventilation capacity of the right lung and a left lung respiration for each breath of the subject. Not only the left lung suction level (first left lung breathing level BL1, second left lung breathing level BL2) indicating the ventilation capacity, but also the magnitude of each of the abdominal breathing and chest breathing on the right side of the subject's trunk, It is different from the above-described embodiments in that control is performed to display the magnitudes of the abdominal breathing and the chest breathing on the left side of the trunk. Hereinafter, specific contents will be described.

  First, with reference to FIG. 28 and FIG. 29, the relationship between the breathing of the subject and the peripheral diameter Rib of the subject's chest and the peripheral diameter Ab of the abdomen will be described. First, it is assumed that the subject's breathing is abdominal breathing. FIG. 28 is a diagram showing the results of capturing time-series changes in the respective peripheral diameters of the chest and abdomen in conjunction with the subject's abdominal breathing with Respitrace (manufactured by A.M.I., USA). As understood from FIG. 28, when the subject's breathing is abdominal breathing, the peripheral diameter Ab of the abdomen changes according to the breathing, while the peripheral diameter Rib of the chest hardly changes. Therefore, in the case of abdominal breathing, the change in the circumference of the subject's chest circumference Rib (the relative value of Rib (measurement value) relative to the Rib reference value indicating the reference level of the Rib measurement value) ΔRib and the circumference of the subject's abdomen ΔRib / ΔAb indicating the ratio of Ab change (relative value of Ab (measured value) to Ab reference value indicating the reference level of the measured value of Ab) ΔAb is less than “1”. The response trace information includes the absolute value (0-P) of the peak value (or bottom value) of the relative value with respect to the reference, and the sum (PP) of the absolute value of the peak value and bottom value of the relative value. It is detected by either. Here, since the determination of the type of breathing is performed for each breath of the subject, the information on the response trace is detected in the form of PP.

  Next, it is assumed that the subject's breathing is chest breathing. FIG. 29 is a diagram showing a result of capturing time-series changes in the peripheral diameters of the chest and abdomen in conjunction with the subject's chest breathing with Respiret (manufactured by A.M.I., USA). When the subject's breathing is thoracic breathing, the change in the peripheral diameter Rib of the chest corresponding to the respiration is larger than the change in the peripheral diameter Ab of the abdomen, and thus the above-described ΔRib / ΔAb exceeds “1”. Condition. Here, ΔRib / ΔAb can be regarded as discrimination information that can discriminate whether the subject's breathing is abdominal breathing or chest breathing.

  In this embodiment, the ratio (= ΔRib / ΔAb) of the change ΔRib in the circumference of the chest of the subject and the change ΔAb in the circumference of the abdomen, and the relative value of the measured value of the bioelectrical impedance Za of the upper trunk to the centering value Za0. It is found that there is a correlation between the value ΔZa and the relative value ΔZb with respect to the centering value Zb0 of the measured value of the bioelectrical impedance Zb in the middle of the trunk, and the relative value ΔZa is determined using an expression representing the correlation. And the value of ΔRib / ΔAb corresponding to the relative value ΔZb is obtained. The degree of the abdominal breathing of the subject is estimated based on the obtained ΔRib / ΔAb value. The centering value Za0 indicates an amplitude reference level for extracting information resulting from respiration from a waveform indicating a change with time of the bioelectrical impedance Za. The centering value Zb0 indicates an amplitude reference level for extracting information resulting from respiration from a waveform indicating a change in bioelectrical impedance Zb with time.

FIG. 30 is a correlation diagram showing the relationship between ΔRib / ΔAb and ΔZb / ΔZa obtained from the measurement data of a plurality of subjects. As can be understood from FIG. 30, a high correlation of correlation coefficient R = 0.651 and P <0.01 is obtained between ΔRib / ΔAb and ΔZb / ΔZa, and the following regression equation (1 ) Holds.
ΔRib / ΔAb = a0 × ΔZb / ΔZa + b0 (1)
a0: regression coefficient, b0: constant.

The regression equation (1) can be modified as follows.
ΔRib / ΔAb = (a0 × ΔZb−ΔZa) / ΔZa + b1 (2)
b1: Constant (= b0 + 1).

  In this embodiment, the value of ΔRib / ΔAb corresponding to the first relative value ΔZaR and the third relative value ΔZbR is obtained using the regression equation (2). This ΔRib / ΔAb can be regarded as an index that can determine the type of breathing on the right side of the subject's trunk. In the present embodiment, the value of ΔRib / ΔAb corresponding to the second relative value ΔZaL and the fourth relative value ΔZbL is obtained using the regression equation (2). This ΔRib / ΔAb value can be regarded as an index that can determine the type of breathing on the left side of the subject's trunk. Details of these will be described later.

  Next, specific contents of the respiration level detection process in the third embodiment will be described. FIG. 31 and FIG. 32 are flowcharts for explaining specific contents of the respiration level detection process in the third embodiment. As shown in FIG. 31, in the respiration level detection process in the present embodiment, after the second right lung respiration level extraction process in step S810, the first relative value ΔZaR (n) and the third relative value ΔZbR (n) are obtained. The right (trunk right) ΔRib / ΔAb estimation calculation process for estimating the corresponding ΔRib / ΔAb (n) is executed (step S815). Further, as shown in FIG. 32, after the second left lung respiration level extraction process in step S860, ΔRib / ΔAb corresponding to the second relative value ΔZaL (n) and the fourth relative value ΔZbL (n) is estimated. It differs from the above-described second embodiment in that ΔRib / ΔAb estimation calculation processing on the left side (left side of the trunk) is executed (step S865). Since the other part is the same as the content of the respiration level detection process in the second embodiment described above, a detailed description is omitted.

  FIG. 33 is a flowchart showing specific contents of the right ΔRib / ΔAb estimation calculation process executed by CPU 170 in step S815. As shown in FIG. 33, the CPU 170 first determines whether or not the value of the first relative value ΔZaR (n) at the n-th sampling timing is “0” or more (step S1000).

  If the result of step S1000 is negative, the CPU 170 determines that the subject's breathing is exhalation, and performs an estimation calculation of ΔRib / ΔAb (n) on the right side at the nth sampling timing (step S1010). More specifically, the CPU 170 executes arithmetic processing according to the above-described regression equation (2), whereby ΔRib / ΔAb (corresponding to the first relative value ΔZaR (n) and the third relative value ΔZbR (n). n). On the other hand, if the result of step S1000 is affirmative, CPU 170 determines that the subject's breathing is inspiration, and sets the value of ΔRib / ΔAb (n) on the right side at the nth sampling timing to an initial value. In this embodiment, when the result of step S1000 is positive, the CPU 170 sets the value of ΔRib / ΔAb (n) on the right side at the n-th sampling timing to “1.0” that is an initial value.

  Next, the CPU 170 determines whether or not the value of ΔRib / ΔAb (n) on the right side is −2.5 or more and 4.5 or less (step S1020). If the result of step S1020 is negative, the CPU 170 sets the value of ΔRib / ΔAb on the right side to the initial value “1.0” and proceeds to step S1030. If the result of step S1020 is affirmative, the CPU 170 proceeds to step S1030 as it is.

  In step S1030, the CPU 170 determines the difference (| ΔRib) between the absolute value of ΔRib / ΔAb (n) on the right side and the absolute value of ΔRib / ΔAb (n−1) on the right side at the immediately preceding (n−1) th sampling timing. It is determined whether / ΔAb (n) | − | ΔRib / ΔAb (n−1) |) is greater than 0.3. When the result of step S1030 is negative, the CPU 170 obtains an average of the right ΔRib / ΔAb (n−1) and the right ΔRib / ΔAb (n) at the immediately preceding n−1th sampling timing, The obtained average value is adopted as ΔRib / ΔAb (n) on the right side at the n-th sampling timing ([ΔRib / ΔAb (n−1) + ΔRib / ΔAb (n)] / 2 → ΔRib / ΔAb (n) ) And proceeds to the next step S1040 (see FIG. 34). On the other hand, if the result of step S1030 is affirmative, the CPU 170 sets the value of ΔRib / ΔAb (n) on the right side at the n-th sampling timing to the initial value “1.0” and proceeds to the next step S1040. move on.

  With reference to FIG. 34, the description of the specific content of the right ΔRib / ΔAb estimation calculation processing will be continued. As shown in FIG. 34, in step S1040, the CPU 170 determines whether or not the first relative value ΔZaR (n) at the nth sampling timing is smaller than “0”. If the result of step S1040 is affirmative, the CPU 170 determines that the subject's breathing is exhalation, and adds 1 to the count value Ni of the previous integration count. More specifically, the CPU 170 counts the number of integrations at the nth sampling timing by adding a value obtained by adding 1 to the count value Ni (n−1) of the number of integrations at the immediately preceding n−1th sampling timing. The value Ni (n) is adopted.

  On the other hand, if the result of step S1040 is negative, the CPU 170 determines that the subject's breathing is inspiration, and initializes the count value Ni of the number of integrations to “0”. That is, in this case, the count value Ni (n) of the number of integrations at the nth sampling timing is set to “0”.

  Subsequently, as illustrated in FIG. 34, the CPU 170 determines again whether or not the first relative value ΔZaR (n) is smaller than “0” (step S1050). If the result of step S1050 is affirmative, the CPU 170 determines the right ΔRib / ΔAb integral value (ΣΔRib / ΔAb (n−1)) at the immediately preceding n−1th sampling timing and the nth sampling timing. By obtaining the sum of ΔRib / ΔAb (n) on the right side, the integral value (ΣΔRib / ΔAb (n)) of ΔRib / ΔAb on the right side at the nth sampling timing is obtained, and the process proceeds to the next step S1060. On the other hand, if the result of step S1050 is negative, that is, if it is determined that the subject's breathing state is inspiration, the CPU 170 sets the aforementioned peak / bottom determination flag F1 (n) to “+1”. Then, the process proceeds to next Step S1060.

  Next, the CPU 170 determines whether or not the count value Ni (n) of the number of integrations at the nth sampling timing is zero (step S1060). If the result of step S1060 is negative, the CPU 170 obtains the integration value [ΣΔRib / ΔAb (n)] of the right side ΔRib / ΔAb at the nth sampling timing and the count value Ni of the number of integrations at the nth sampling timing. By dividing by (n), an average value of ΔRib / ΔAb on the right side is obtained. On the other hand, when the result of step S1060 is positive, the CPU 170 determines the average value of [Delta] Rib / [Delta] Ab on the right side at the immediately preceding (n-1) th sampling timing ([[Sigma] [Delta] Rib / [Delta] Ab (n-1)] / Ni (n-1). )) Is adopted as the average value of ΔRib / ΔAb on the right side at the n-th sampling timing. Thus, the right ΔRib / ΔAb estimation calculation process in step S815 of FIG. 31 ends.

  When the subject's breathing is abdominal breathing, the average value ([ΣΔRib / ΔAb] / Ni) of ΔRib / ΔAb described above changes as shown in FIG. In FIG. 35, when the value (average value) of ΔRib / ΔAb in exhalation is 1.0 or less, it is estimated that abdominal breathing is performed, and when it exceeds 1.0, it is estimated that chest breathing is performed. That is. Note that the specific contents of the ΔRib / ΔAb estimation calculation process on the left side (left side of the trunk) in step S865 in FIG. 32 are the same as the contents of the above-described right ΔRib / ΔAb estimation calculation process, and thus detailed description is given here. Description is omitted.

  Next, a respiration level display process executed by the CPU 170 will be described. In this embodiment, the CPU 170 performs the first right lung respiration level BR1, the first left lung respiration level BL1, the second right lung respiration level BR2, and the second left respiration for each respiration of the subject. In addition to controlling the display unit 160 to display the pulmonary respiration level BL2 (the same contents as in the second embodiment described above), as shown in FIG. 36, as shown in FIG. The display unit 160 displays the magnitude of each of the chest breaths as a fifth bar graph BG5 and displays the magnitude of each of the left abdominal breath and the chest breath as a sixth bar graph BG6. This is different from the second embodiment described above in that it is controlled. More specifically, it is as follows.

  First, a display mode using the fifth bar graph BG5 will be described. In the present embodiment, the CPU 170 determines the number of stages of the fifth bar graph BG5 to be colored and displayed in accordance with the first right lung respiration level BR1 in one respiration immediately before the respiration level detection process. . Then, the CPU 170 assigns the number of stages of the fifth bar graph BG5 to be colored and displayed to the chest type and the abdomen type according to the average value of ΔRib / ΔAb on the right side of the trunk in the last one breath.

  Next, the display mode by the sixth bar graph BG6 will be described. In the present embodiment, the CPU 170 determines the number of steps of the sixth bar graph BG6 to be colored and displayed according to the first left lung respiration level BL1 in the last respiration detected in the respiration level detection process. . Then, the CPU 170 assigns the number of stages of the sixth bar graph BG6 to be colored and displayed to the chest type and the abdomen type according to the average value of ΔRib / ΔAb on the left side of the trunk in the last one breath.

  As described above, in the present embodiment, the CPU 170 performs the right lung respiration level (the first right lung respiration level BR1, the second respiration level indicating the ventilation ability of the right lung in the one respiration) for each respiration of the subject. Right lung respiration level BR2) and left lung absorption level (first left lung respiration level BL1, second left lung respiration level BL2) indicating the ventilation capacity of the left lung, as well as abdominal respiration on the right side of the subject's trunk And chest breathing, and the abdominal breathing and chest breathing on the left side of the trunk, are controlled to display the right breathing level and the left lung breathing level. It is possible to easily recognize the difference between the degree of abdominal breathing on the right side of the trunk and the degree of abdominal breathing on the left side of the trunk. Thus, the subject can more clearly recognize the difference between the left and right ventilation capabilities.

  For example, for each breath of the subject, the first right lung respiratory level BR1, the first left lung respiratory level BL1, and the level of abdominal breathing on the right side of the trunk for each breath of the subject. The second right lung respiration level BR2 and the second left lung respiration level BL2 may not be displayed while the abdominal breathing degree on the left side of the trunk is displayed. That is, the second right lung breathing level BR2 and the second left lung breathing level BL2 are not measured, and the first right lung breathing level BR1, the first left lung breathing level BL1, and the right abdominal breathing of the trunk right side are not measured. It may be an aspect in which the degree and the degree of abdominal breathing on the left side of the trunk are measured. Also, for example, for each breath of the subject, the second right lung breathing level BR2, the second left lung breathing level BL2, the degree of abdominal breathing on the right side of the trunk, and the abdominal style on the left side of the trunk While the degree of respiration is displayed, the first right lung respiration level BR1 and the first left lung respiration level BL1 may not be displayed. That is, the first right lung breathing level BR1 and the first left lung breathing level BL1 are not measured, the second right lung breathing level BR2, the second left lung breathing level BL2, and the right abdominal breathing of the trunk right side. It may be an aspect in which the degree and the degree of abdominal breathing on the left side of the trunk are measured.

<D: Fourth Embodiment>
In the fourth embodiment, a case where a Lissajous figure is displayed will be described. Since the hardware configuration of the biometric apparatus is basically the same as that described in the first embodiment, the same reference numerals as those in the first embodiment are used and description thereof is omitted.

<D-1: Display of Lissajous figure for right lung and Lissajous figure for left lung>
The Lissajous figure for the right lung showing the change over time of the measured value of the first bioelectric impedance ZaR and the measured value of the third bioelectrical impedance ZbR, the measured value of the second bioelectrical impedance ZaL and the fourth bioelectrical impedance ZbL By displaying the Lissajous figure for the left lung indicating the change over time of the measured value, it is possible to notify the subject of the type of breathing and its size. Hereinafter, a Lissajous figure for the right lung having the X axis as the third bioelectrical impedance ZbR, the Y axis as the first bioelectrical impedance ZaR, the X axis as the fourth bioelectrical impedance ZbL, and the Y axis as the second bioelectrical impedance A case of a Lissajous figure for the left lung having an impedance ZaL will be described as an example.

  In the case of thoracic respiration, as shown in FIG. 10, the bioelectrical impedance Za at the upper trunk and the bioelectrical impedance Zb at the middle trunk change in an increasing direction in inspiration, and the bioelectrical impedance Za in the upper trunk in exhalation. In addition, the bioelectric impedance Zb in the middle of the trunk changes in a decreasing direction. Therefore, when the ratio of chest breathing to one breath is extremely high, for example, as shown in FIG. 37, the locus of the Lissajous figure for one breath for the right lung or the left lung becomes a straight line that rises to the right. Also, if the chest breathing is shallow, the locus of the Lissajous figure becomes small, and if the chest breathing is deep, the locus of the Lissajous figure becomes large.

  On the other hand, in the case of abdominal breathing, as shown in FIG. 9, the bioelectrical impedance Za of the upper trunk and the bioelectrical impedance Zb of the middle trunk change in an increasing direction during inspiration, and the upper trunk of the trunk during exhalation. The bioelectric impedance Za changes in the decreasing direction, while the bioelectric impedance Zb in the middle of the trunk changes in the increasing direction. Therefore, when the subject's breathing includes abdominal breathing, for example, as shown in FIG. 38, the trajectory of the Lissajous figure for one breath for the right lung or the left lung becomes a bent shape.

  Note that the Lissajous figure shown in FIG. 38 is a case where the ratio of the chest breathing and the abdominal breathing to one breath is 50%. In this case, the locus of the Lissajous figure has a boomerang shape ("<" shape), and the shape of the locus is almost symmetrical vertically. However, if the proportion of the abdominal breathing is lower than that of the chest breathing, the Lissajous locus will have a larger proportion of the straight line that goes up to the right corresponding to the trajectory in the case of the chest breathing, and the portion bent from there The proportion occupied by the straight line portion (lower straight line in FIG. 38) decreases. On the other hand, if the proportion of abdominal breathing is higher than that of chest breathing, the locus of the Lissajous figure becomes smaller in the proportion of the straight line that goes up to the right corresponding to the locus of chest breathing, and then bends from there. The proportion of the part increases. In this way, when the subject's breathing includes abdominal breathing, the trajectory of the Lissajous figure varies in bending shape depending on the ratio of chest breathing and abdominal breathing.

  In theory, when the ratio of abdominal breathing to one breath is 100%, the locus of the Lissajous figure is a straight line inclined in the opposite direction to the locus of chest breathing (in the case of FIG. 38, the right A downward straight line). However, for example, even when the abdomen is recessed or inflated with the breath stopped and no chest breathing performed, the lungs contract and expand with the diaphragm above and below, Except when the diaphragm does not function at all due to disease or the like, chest breathing is always included when the subject breathes. Therefore, in fact, no matter how high the proportion of abdominal breathing per breath, the Lissajous figure always includes a straight line part that rises to the right corresponding to the path for chest breathing. It becomes a bent shape. Further, as shown in FIG. 38, how much the bent portion (approximate straight line LN2) is bent with respect to the straight line part rising to the right (approximate straight line LN1) corresponding to the locus in the case of chest breathing. The bend angle AG is smaller when the abdominal breathing is shallow, and is larger when the abdominal breathing is deep. Also, in the case of abdominal breathing, the trajectory of the Lissajous figure becomes smaller when breathing is shallow, and the trajectory of the Lissajous figure becomes larger when breathing is deep.

  In addition, although the Lissajous figure for 1 breath was shown in FIG.37 and FIG.38, as shown in FIG.39 and FIG.40, the Lissajous figure which shows the mode of several times of breathing continuously may be sufficient. When the proportion of chest breathing is extremely high, the Lissajous figure shown in FIG. 39 is obtained. When the subject's breathing includes abdominal breathing, the Lissajous figure shown in FIG. 40 is obtained.

  In addition to chest-type breathing and abdominal-type breathing, there is draw-in breathing in which exhalation and inhalation are performed while maintaining a depressed state. Draw-in breathing can effectively train inner trunk muscles that are not often used in everyday life (for example, the transverse abdominal muscles and the spine upright muscles). Strengthening the inner muscle not only enhances breathing function, but also strengthens the muscles that support the spine, making it easier for the muscles of the trunk to exert their power, leading to enhancement of motor functions and the like. For example, draw-in breathing has been incorporated into athlete training for the purpose of improving motor function. In physical therapy and rehabilitation, draw-in breathing is used to improve low back pain and prevent low back pain. Draw-in breathing is also effective for dieting.

  In the case of draw-in breathing, as shown in FIG. 41, the bioelectrical impedance Za at the upper trunk and the bioelectrical impedance Zb at the middle trunk change in an increasing direction in inspiration, and the bioelectrical impedance Za in the upper trunk in exhalation and Both the bioelectrical impedance Zb in the middle of the trunk change in the decreasing direction. This change is the same as for chest breathing. This is because in the case of draw-in breathing, exhalation and inhalation are performed by chest breathing while maintaining a state where the abdomen is recessed. However, in the case of draw-in breathing, since the abdomen is pressed to dent the abdomen, the amplitude reference level of the bioelectrical impedance Zb in the middle of the trunk is higher than that in the case of the chest breathing as shown in FIG. Become. For this reason, when comparing the Lissajous figures in the case of draw-in respiration and chest respiration, as shown in FIG. 42, the trajectories of both are linearly rising to the right, but the bioelectrical impedance Zb in the middle of the trunk is assigned. The locus is shifted in the axial direction (in FIG. 42, the X-axis direction to which the third bioelectric impedance ZbR on the right side of the trunk is assigned). Also, if the draw-in breathing is shallow, the locus of the Lissajous figure becomes small, and if the draw-in breathing is deep, the locus of the Lissajous figure becomes large.

FIG. 43 is a flowchart showing the contents of the Lissajous figure display process.
In the flowchart shown in the figure, the processing from step S1101 to S1107 is the same as the processing from step S700 to S760 of the respiration level detection processing (FIGS. 22 and 23) described in the second embodiment. That is, also in the present embodiment, when the sampling timing is reached (step S1101: YES), the CPU 170 controls the bioelectrical impedance measurement unit 200 to measure the first bioelectrical impedance ZaR and the third bioelectrical impedance ZbR (step S1101). S1102, S1103). Further, the CPU 170 performs a smoothing process on the measured value of the first bioelectric impedance ZaR and the measured value of the third bioelectric impedance ZbR (step S1104). Next, the CPU 170 controls the bioelectrical impedance measurement unit 200 to measure the second bioelectrical impedance ZaL and the fourth bioelectrical impedance ZbL (steps S1105 and S1106). Further, the CPU 170 performs a smoothing process on the measured value of the second bioelectrical impedance ZaL and the measured value of the fourth bioelectrical impedance ZbL (step S1107).

  Thereafter, the CPU 170 generates display data of a Lissajous figure for the right lung having the X axis as the third bioelectrical impedance ZbR and the Y axis as the first bioelectrical impedance ZaR (step S1108). Further, the CPU 170 generates display data of a Lissajous figure for the left lung having the X axis as the fourth bioelectrical impedance ZbL and the Y axis as the second bioelectrical impedance ZaL (step S1109). Here, the second storage unit 130 is provided with a Lissajous figure drawing area. The Lissajous figure drawing area is a storage area for temporarily storing display data of a Lissajous figure for the right lung and a Lissajous figure for the left lung displayed on the display unit 160. For example, when generating display data for a Lissajous figure for the right lung, the CPU 170 measures the measured value (X coordinate value) of the third bioelectrical impedance ZbR and the measured value of the first bioelectrical impedance ZaR in the Lissajous figure drawing area. Dots are plotted at positions determined by (Y coordinate value), and the locus of the Lissajous figure for the right lung is updated. When generating the display data of the Lissajous figure for the left lung, the CPU 170 measures the measured value (X coordinate value) of the fourth bioelectrical impedance ZbL (measured value of the second bioelectrical impedance ZaL) in the Lissajous figure drawing area ( Dots are plotted at positions determined by the Y coordinate value), and the locus of the Lissajous figure for the left lung is updated.

  Thereafter, the CPU 170 reads the display data of the two Lissajous figures for the right lung and the left lung from the Lissajous figure drawing area and outputs them to the display unit 160. As a result, two Lissajous figures for the right and left lungs are displayed on the display unit 160 (step S1110). Since the processing shown in FIG. 10 is performed at each sampling timing, the trajectories of the two Lissajous figures for right lung and left lung are updated at each sampling timing in steps S1108 and S1109. The display of the two Lissajous figures is also updated at each sampling timing.

  Therefore, when the subject is breathing, two Lissajous figures for the right lung and the left lung are displayed on the display unit 160 in real time. For example, when the proportion of chest breathing is extremely high, the Lissajous figure shown in FIGS. 37 and 39 is displayed as the Lissajous figure for the right lung. When the subject's breathing includes abdominal breathing, the Lissajous figure shown in FIG. 38 or 40 is displayed as the Lissajous figure for the right lung. Further, when the subject's breathing gradually changes from the chest type to the abdominal type, for example, as shown in FIG. 44, the locus of the Lissajous figure is gradually bent from the straight line rising to the right side toward the right side. Elongates and changes to a bent shape.

  In addition, two Lissajous figures for the right and left lungs may be displayed side by side, but in order to make it easier to grasp the difference in ventilation capacity between the left and right lungs, they are overlapped as shown in FIG. It is good to display. In this case, the CPU 170 only has to draw the Lissajous figure for the right lung and the Lissajous figure for the left lung in the Lissajous figure drawing area. In addition, when two Lissajous figures for the right and left lungs are displayed in a superimposed manner, the Lissajous figure for the right lung and the Lissajous figure for the left lung are displayed so that they can be easily distinguished from each other. It is preferable to change the display mode of the trajectory. For example, when the CPU 170 generates display data of two Lissajous figures for the right lung and the left lung, the locus color is set to blue for the Lissajous figure for the right lung, and the locus for the Lissajous figure for the left lung. The color of can be red. In addition to changing the color of the trajectory, the CPU 170 can change, for example, the thickness of the line indicating the trajectory and the line type (for example, a solid line and a broken line). When two Lissajous figures for the right lung and the left lung are displayed side by side, the display mode of the trajectory of both may be changed.

  As shown in FIG. 46, the difference between the two Lissajous figures for the right lung and the left lung may be highlighted. In this case, the CPU 170, for example, the right lung Lissajous figure determined by the measured value (X coordinate value) of the third bioelectrical impedance ZbR and the measured value (Y coordinate value) of the first bioelectrical impedance ZaR at each sampling timing. Coordinates on Lissajous figure for left lung determined by upper coordinates (XR, YR), measured value (X coordinate value) of fourth bioelectrical impedance ZbL and measured value (Y coordinate value) of second bioelectrical impedance ZaL Compare with (XL, YL). Then, when the two are different, the CPU 170 generates display data of a bar (straight line) connecting the coordinates (XR, YR) and the coordinates (XL, YL). Thus, if the difference between the two Lissajous figures for the right lung and the left lung can be highlighted and displayed, it becomes easy to grasp the difference in the ventilation capacity between the left and right lungs.

  Note that the CPU 170 may change the color of the bar between the expiration phase and the inspiration phase. In the measurement waveform of the first bioelectrical impedance ZaR shown in FIG. 24, the portion above the first centering value ZaR0 is the inspiratory phase, and the portion below the first centering value ZaR0 is the expiratory phase. Therefore, for example, if the average value of the first centering value ZaR0 in the immediately preceding one breath is a straight line portion indicated by a two-dot difference line in FIG. 46, the color of the bar may be changed above and below this straight line. However, in order to change the color of the bar between the expiration phase and the inspiration phase in this way, it is necessary to perform the first centering process described in the first embodiment for the first bioelectric impedance ZaR. Alternatively, the second centering process described in the first embodiment needs to be performed on the second bioelectrical impedance ZaL instead of the first bioelectrical impedance ZaR.

  Further, the CPU 170 compares the coordinates (XR, YR) and the coordinates (XL, YL) at the same sampling timing, and determines whether the color obtained by subtracting the other X coordinate value from one X coordinate value is positive or negative. Or the bar color may be changed depending on whether the solution obtained by subtracting the other Y coordinate value from one Y coordinate value is positive or negative. Further, the CPU 170 may compare the coordinates (XR, YR) and the coordinates (XL, YL) at the same sampling timing, and change the color tone of the bar according to the distance between the two coordinates. For example, the color can be darkened if the distance between the two coordinates is large, and the color can be lightened if the distance between the two coordinates is small. Further, instead of displaying the bar, the CPU 170 may fill the area displaying the bar with a light color.

  In addition, the CPU 170 obtains a difference area between the two Lissajous figures for the right lung and the left lung (the area where the bar is displayed in FIG. 46), and how much the ventilation capacity is in the left and right lungs from the size of the difference area. For example, the difference may be classified into five levels and notified to the subject. In this case, the sum of bars (difference lines) may be used instead of the difference area. Further, as shown in FIG. 47, the CPU 170 calculates an intermediate coordinate between the coordinates (XR, YR) and the coordinates (XL, YL) at each sampling timing, plots a dot at this position, and for the right lung and the left lung The average value of the two Lissajous figures may be displayed. In addition, when the CPU 170 displays two Lissajous figures for the right lung and the left lung side by side, for example, a portion different from the locus of the left lung Lissajous figure among the locus of the right lung Lissajous figure is thicker. While highlighting with a line, a portion different from the locus of the Lissajous figure for the right lung among the locus of the Lissajous figure for the left lung may be highlighted with a thicker line.

  As shown in FIGS. 37 and 39, when the proportion of chest breathing is extremely high, the locus of the Lissajous figure for the right lung or the left lung becomes a straight line that rises to the right. Also, if the chest breathing is shallow, the locus of the Lissajous figure becomes small, and if the chest breathing is deep, the locus of the Lissajous figure becomes large. On the other hand, as shown in FIGS. 38 and 40, when the subject's breathing includes abdominal breathing, the locus of the Lissajous figure for the right lung or the left lung becomes a bent shape. In the case of abdominal breathing, if the breathing is shallow, the locus of the Lissajous figure becomes small and the bending angle AG becomes small. If the breathing is deep, the locus of the Lissajous figure becomes large and the bending angle AG becomes large.

  Thus, the shape of the locus of the Lissajous figure is different between the chest breathing and the abdominal breathing. Further, the size and shape of the locus of the Lissajous figure changes depending on the magnitude (depth) of chest-type breathing and abdominal-type breathing. Therefore, the subject can look at the Lissajous figure to determine whether their current breathing is chest or abdominal breathing, or whether their current breathing is more of the chest or abdominal breathing. Can be grasped. In addition, the magnitude of chest breathing and abdominal breathing can be grasped from the Lissajous figure.

  In addition, when the subject performs chest-type breathing training, the subject may breathe consciously so that the locus of the Lissajous figure becomes a straight line that rises to the right and the size thereof increases. Further, when abdominal breathing exercises are performed, breathing may be performed with an awareness that the locus of the Lissajous figure is bent and the size and bending angle AG are increased. If breathing training can be performed while looking at the Lissajous figure in this way, the training can be advanced while confirming whether or not chest breathing and abdominal breathing are correctly performed and their sizes as needed.

  In addition, as shown in FIG. 42, in the case of draw-in breathing, the locus of the Lissajous figure for the right lung and the left lung becomes a straight line that rises to the right as in the case of chest breathing, but the position of the locus is Shifts in the X-axis direction. Therefore, the subject can grasp whether or not his / her respiration is a draw-in respiration by looking at the Lissajous figure. In the case of draw-in breathing, the trajectory of the Lissajous figure becomes smaller if the breathing is shallow, and the trajectory of the Lissajous figure becomes larger if the breathing is deep. Therefore, the magnitude of the draw-in breath can also be grasped from the Lissajous figure. Also, in the case of draw-in breathing, training can be carried out while confirming whether or not the draw-in breathing is correctly performed and the size thereof by performing training while looking at the Lissajous figure.

  If the two Lissajous figures for the right and left lungs can be displayed as described above, the subject will be able to display his / her current breathing type and size, as well as chest and abdominal breathing and draw-in. Whether or not breathing is correct can be grasped for each of the left and right lungs. In addition, it is possible to objectively grasp the type and size of respiration, or whether chest respiration, abdominal respiration, and draw-in respiration are correctly performed based on the measured value of bioelectrical impedance. Also, by comparing the two Lissajous figures, it is possible to easily grasp the difference in ventilation capacity between the left and right lungs.

  Further, by displaying two Lissajous figures for the right lung and the left lung, it becomes possible to perform breathing training for each of the left and right lungs. In the case of a healthy person, there is almost no difference in ventilation capacity between the left and right lungs. For example, a person with a disease in one lung has a large difference in ventilation capacity between the left and right lungs. Also, those who have experienced lung disease in the past may have differences in ventilation capacity between the left and right lungs. For example, if you want to increase the ventilation capacity of the left lung, such as when the ventilation capacity of the left lung is lower than the right lung, turn the left arm behind the right shoulder and push the left elbow back with the right hand to the left lung. By giving a load and breathing while maintaining this state, the ventilation ability of the left lung can be intensively trained.

  In addition, respiratory training (for example, transverse abdominal muscles, diaphragm, internal intercostal muscles, external intercostal muscles, sternocleidomastoid muscles, anterior oblique muscles, mid oblique muscles, posterior oblique muscles) , Straight abdominal muscle, internal oblique muscle, external oblique muscle, etc.) can be effectively trained. In particular, the transverse abdominal muscles included in the respiratory muscles are trunk muscles that greatly affect not only breathing but also motor function. In addition, draw-in breathing can reinforce not only the respiratory muscles but also the inner muscles of the trunk, such as the spine standing muscles. Therefore, breathing exercises are effective not only for improving respiratory function, but also for strengthening motor function, improving / preventing back pain, and dieting. Also, for example, breathing exercises such as taking deep breaths (deep abdominal breathing) or making exhalation longer than inspiration can lead to a more relaxed state by increasing the function of parasympathetic nerves. It also has the effect of improving mental and physical health.

  Respiratory training includes, for example, rehabilitation performed for the purpose of recovering reduced respiratory function in patients with respiratory diseases, training performed for the purpose of strengthening motor functions by athletes, and respiratory function and physical and mental health for healthy individuals. Training that is performed for the purpose of improving the state, training that is performed by a healthy person for the purpose of improving respiratory function that has decreased due to smoking, lifestyle-related diseases, lack of exercise, aging, and the like.

  Further, in the above description, the Lissajous figure for the right lung having the X axis as the third bioelectrical impedance ZbR and the Y axis as the first bioelectrical impedance ZaR, the X axis as the fourth bioelectrical impedance ZbL, and the Y axis The Lissajous figure for the left lung with the second bioelectrical impedance ZaL as an example is illustrated, but the Lissajous figure for the right lung or the left lung may be one in which the X axis and the Y axis are interchanged. For example, FIG. 48 shows a Lissajous figure for the right lung (in the case of abdominal breathing) in which the X axis is the first bioelectrical impedance ZaR and the Y axis is the third bioelectrical impedance ZbR. The trajectory of the Lissajous figure becomes a bent shape even if they are replaced. In addition, in the Lissajous figure in which the X axis and the Y axis are switched in this way, when the subject's breathing gradually changes from the chest type to the abdominal type, for example, as shown in FIG. From the straight line shape, the lower part gradually expands while bending upward and changes to a bent shape. Further, the Lissajous figure for the right lung and the left lung may be obtained by inclining the X axis and the Y axis by 45 degrees as shown in FIG. In short, the Lissajous figure for the right lung may be a Lissajous figure in which one of the two axes orthogonal to each other is the first bioelectrical impedance ZaR and the other axis is the third bioelectrical impedance ZbR. Further, the Lissajous figure for the left lung may be a Lissajous figure in which one of the two orthogonal axes is the second bioelectrical impedance ZaL and the other axis is the fourth bioelectrical impedance ZbL.

<D-2: Centering of display position>
The display positions of the two Lissajous figures for the right lung and the left lung can be centered by adjusting the display range of the X axis and the display range of the Y axis. Hereinafter, a Lissajous figure for the right lung having the X axis as the third bioelectrical impedance ZbR, the Y axis as the first bioelectrical impedance ZaR, the X axis as the fourth bioelectrical impedance ZbL, and the Y axis as the second bioelectrical impedance A case of a Lissajous figure for the left lung having an impedance ZaL will be described as an example.

  The CPU 170 detects the maximum value and the minimum value of the measurement value of the first bioelectrical impedance ZaR, for example, for each breath, and acquires both as the first amplitude value (first maximum value, first minimum value). Also, the CPU 170 detects the maximum value and the minimum value for each breath for the measured value of the second bioelectrical impedance ZaL, and acquires both as the second amplitude values (second maximum value, second minimum value). . Similarly, the CPU 170 detects the maximum value and the minimum value for each measurement of the measurement value of the third bioelectric impedance ZbR and the measurement value of the fourth bioelectric impedance ZbL, and the third amplitude value (the third maximum value, (3rd minimum value) and 4th amplitude value (4th maximum value, 4th minimum value) are acquired. Thereafter, the CPU 170 adjusts the display range of the X axis using the third amplitude value and the fourth amplitude value, and adjusts the display range of the Y axis using the first amplitude value and the second amplitude value.

  For example, when the width in the X-axis direction of the Lissajous figure display area 160A for displaying the Lissajous figure on the display unit 160 is 10, the CPU 170 has four values (third maximum value, The difference between the maximum value and the minimum value of the third minimum value, the fourth maximum value, and the fourth minimum value is about 8 to 9, and all four values are displayed in the Lissajous figure display area 160A. As described above, the size and position in the X-axis direction of the two Lissajous figures for the right lung and the left lung drawn in the Lissajous figure drawing area are adjusted. Similarly, when the width of the Lissajous figure display region 160A in the Y-axis direction is 10, the CPU 170 has four values (first maximum value, first minimum value, and second maximum value) related to the first amplitude value and the second amplitude value. Value, second minimum value), and the difference between the maximum value and the minimum value is about 8 to 9, and the four values are displayed in the Lissajous figure display area 160A. The size and position in the Y-axis direction of the two Lissajous figures for the right lung and left lung drawn in the region are adjusted.

  In this way, for example, as shown in FIG. 50, two Lissajous figures for the right lung and the left lung can be displayed in the Lissajous figure display area 160A with just the right size. Also, two Lissajous figures for the right lung and left lung can be displayed in the center of the Lissajous figure display area 160A. This makes it easy to see the Lissajous figure. The timing for adjusting the display range of the two axes (that is, the timing for performing centering) can be arbitrarily determined. However, since it is desirable that the entire trajectory for at least one breath fits in the Lissajous figure display area 160A, the CPU 170 may acquire the first to fourth amplitude values from the measured waveform for one breath or more.

  Incidentally, as shown in FIG. 42, in the case of draw-in breathing, the locus of the Lissajous figure for the right lung and the left lung is a straight line that rises to the right as in the case of the chest breathing, but the position of the locus is Shifts in the X-axis direction. Here, if centering is frequently performed, two Lissajous figures are always displayed in the center of the Lissajous figure display area 160A, so that it becomes impossible to distinguish between draw-in breathing and chest-type breathing from the Lissajous figure. In order to prevent this, centering in the X-axis direction should not be performed so much.

  That is, the process of adjusting the Y-axis display range using the first amplitude value and the second amplitude value is referred to as the first range adjustment process, and the X-axis display range is adjusted using the third amplitude value and the fourth amplitude value. When the process to be performed is the second range adjustment process, the CPU 170 may make the frequency of performing the second range adjustment process less than the frequency of performing the first range adjustment process. In this case, for example, the first range adjustment process may be performed every breath, while the second range adjustment process may be performed only once at the start of measurement or the like and not performed thereafter. Further, the first range adjustment process may be performed every breath, or the second range adjustment process may be performed every 30 breaths. Further, the first range adjustment process may be performed every 8 seconds, while the second range adjustment process may be performed every 5 minutes.

  Thus, if centering in the X-axis direction is not performed so much, even if the shape of the locus of the Lissajous figure is the same, the display position of the locus is the X-axis direction in the case of draw-in breathing and the case of chest-type breathing. Will shift to. Therefore, it becomes possible to distinguish between draw-in breathing and chest breathing from the Lissajous figure. Moreover, the power consumption of the biometric apparatus 1 can be reduced by the amount that the frequency of performing the second range adjustment process is reduced. In addition, although the frequency is low, the second range adjustment process is also performed, so that two Lissajous figures for the right lung and the left lung are displayed in a size that is just right for the Lissajous figure display area 160A. Or the Lissajous figure display area 160A.

  The bioelectrical impedance Zb in the middle of the trunk is less susceptible to artifacts due to the movement of the extremities such as the arms, and the variation range of the measured value is relatively stable, compared to the bioelectrical impedance Za in the upper trunk. For this reason, the Lissajous figure for the right lung and the left lung can be displayed in the Lissajous figure display area 160A without performing centering in the X-axis direction to which the third bioelectric impedance ZbR and the fourth bioelectric impedance ZbL are assigned so frequently. There is almost no problem such as not fit in.

  Further, a Lissajous figure for the right lung having the X axis as the first bioelectric impedance ZaR and the Y axis as the third bioelectric impedance ZbR, the X axis as the second bioelectric impedance ZaL, and the Y axis as the fourth bioelectricity In the case of a Lissajous figure for the left lung having an impedance ZbL, centering in the Y-axis direction should not be performed so much. In short, of the two axes orthogonal to each other, the frequency of centering in the axial direction to which the third bioelectric impedance ZbR and the fourth bioelectric impedance ZbL are assigned is expressed as the first bioelectric impedance ZaR and the second bioelectric impedance ZaL. What is necessary is just to make it less than the frequency of centering about the allocated axial direction. 50 shows a Lissajous figure in the case of abdominal breathing, it may be a Lissajous figure in the case of chest breathing or draw-in breathing.

  In addition, the bioelectrical impedance Za of the upper trunk is relatively large in variation range compared to the bioelectrical impedance Zb of the middle trunk, because this is largely affected by artifacts due to the movement of the extremities such as arms. Even if this is ignored and the frequency of centering is reduced, it does not matter much. Therefore, the first bioelectrical impedance ZaR and the second bioelectrical impedance are calculated at a frequency (for example, every 30 breaths or every 5 minutes) in the axial direction to which the third bioelectrical impedance ZbR or the fourth bioelectrical impedance ZbL is assigned. Centering in the axial direction to which ZaL is assigned may be performed. That is, the frequency of centering is made the same in the axial direction to which the third bioelectrical impedance ZbR or the fourth bioelectrical impedance ZbL is assigned and the axial direction to which the first bioelectrical impedance ZaR or the second bioelectrical impedance ZaL is assigned, The time interval for centering may be extended every 30 breaths, every 5 minutes, or the like.

<D-3: Trajectory display process>
As shown in FIG. 39 and FIG. 40, in the case of a Lissajous figure that continuously shows a plurality of breaths, it is difficult to grasp the latest one-breath trajectory if the trajectory display mode is the same. Therefore, for the right and left lung Lissajous figures, the display mode of the trajectory may be changed between the latest one breath and the other past breaths. Hereinafter, the case of the Lissajous figure for the right lung will be described as an example, but the display mode of the trajectory can also be changed for the Lissajous figure for the left lung by the same method as that for the Lissajous figure for the right lung.

  For example, when generating the display data of the Lissajous figure for the right lung, the CPU 170 darkens the color of the latest one respiration trajectory and changes the colors of other past respiration trajectories as shown in FIG. Can be thinned. Further, the CPU 170 may make the latest one respiration trajectory a solid line, and other past respiration trajectories may be a dotted line. The CPU 170 may change the color of the trajectory between the latest one breath and the other past breaths. For example, the CPU 170 determines whether or not a new one breath has started based on the measurement waveforms of the first bioelectric impedance ZaR and the second bioelectric impedance ZaL, and when the new one breath starts, the newly started breath The trajectory color for is changed to red, and the color of the previous respiratory trajectory is changed from red to blue.

  The CPU 170 may change the display mode of the trajectory of the Lissajous figure for the right lung or the left lung according to the elapsed time. For example, if the color of the trajectory becomes lighter as the elapsed time increases, the new trajectory becomes darker because the new trajectory is darker. In addition, the Lissajous figure is not limited to that shown in FIG. 51. For example, the X-axis and the Y-axis are interchanged, or the X-axis and the Y-axis are rotated by an arbitrary angle while maintaining an orthogonal state. It may be. 51 shows a Lissajous figure in the case of abdominal breathing, it may be a Lissajous figure in the case of chest breathing or draw-in breathing.

<D-4: Assist display>
As shown in FIG. 52, a Lissajous figure TRL for the right lung showing a target breathing state may be superimposed on the Lissajous figure MRL for the right lung showing the breathing state of the subject. In the following, the case of the Lissajous figure for the right lung will be described as an example, but the Lissajous figure for the left lung also shows the target breathing state in the same manner as the Lissajous figure for the right lung. It is possible to display the Lissajous figure for use. In this chapter, the Lissajous figure for the right lung indicating the state of breathing of the subject is referred to as an actually measured Lissajous figure MRL, and the Lissajous figure for the right lung indicating the state of target breathing is referred to as a target Lissajous figure TRL. .

  The target Lissajous figure TRL can be generated by processing a past Lissajous figure MRL of the subject such as a measured Lissajous figure MRL indicating the state of one breath immediately before the subject. For example, when the subject is practicing chest breathing or draw-in breathing, the CPU 170 increases the size of the actually measured Lissajous figure MRL (straight-up linear trajectory) indicating the state of the last breathing by 1.1 times. Or the like, and this can be used as display data for the target Lissajous figure TRL. When the subject is performing abdominal breathing exercises, the CPU 170 enlarges the size of the measured Lissajous figure MRL (bent shape trajectory) indicating the state of one breath immediately before by a predetermined magnification, The display data of the target Lissajous figure TRL can be generated by adjusting the size of the angle AG.

  Further, the CPU 170 displays the target Lissajous figure TRL in the Lissajous figure display area 160A, while showing the current breathing state of the subject based on the measured value of the first bioelectrical impedance ZaR and the measured value of the third bioelectrical impedance ZbR. Display data of the actually measured Lissajous figure MRL to be generated is generated and displayed on the Lissajous figure display area 160A so as to overlap the target Lissajous figure TRL. In this way, the subject can perform breathing training on the right lung while comparing the measured Lissajous figure MRL and the target Lissajous figure TRL. In addition, the subject can acquire the target respiration by performing respiration while keeping the trajectory of the actually measured Lissajous figure MRL coincident with the trajectory of the target Lissajous figure TRL.

  In addition, the CPU 170 does not process the past measured Lissajous figure MRL to generate the target Lissajous figure TRL, but the type of breathing (chest breathing, abdominal breathing, draw-in breathing, etc.) that the subject wants to perform and its size. A target Lissajous figure TRL corresponding to the size can also be generated. For example, as a respiratory training menu for the right lung (or both lungs), it is stipulated that after a small-sized chest breath is performed once, a medium-sized abdominal breath is performed once. The CPU 170 generates and displays a target Lissajous figure TRL corresponding to a small-sized chest respiratory, and before the subject completes the first breath and performs the next breath, A target Lissajous figure TRL corresponding to a medium-sized abdominal breath is generated and displayed. If the timing for displaying the target Lissajous figure TRL is controlled, the subject's breathing rhythm can be instructed.

  The CPU 170 may change the display mode (for example, color, line type, etc.) of the trajectory between the actually measured Lissajous figure MRL and the target Lissajous figure TRL so that both can be easily distinguished. Further, as shown in FIG. 53, the CPU 170 may display a bar on a portion that differs between the locus of the actually measured Lissajous figure MRL and the locus of the target Lissajous figure TRL, and highlight the difference between the two. Further, the CPU 170 obtains the difference area between the actually measured Lissajous figure MRL and the target Lissajous figure TRL (the area where the bar is displayed in FIG. 53), and ranks how much the two differ from the size of the difference area, for example, in five levels. You may divide and alert | report to a test subject. In this case, the sum of bars (difference lines) may be used instead of the difference area.

  Further, it is not always necessary to display the measured Lissajous figure MRL and the target Lissajous figure TRL in an overlapping manner, and both may be displayed side by side. Further, the measured Lissajous figure MRL and the target Lissajous figure TRL are not limited to those shown in FIGS. 52 and 53. For example, the X axis and the Y axis can be maintained while maintaining the orthogonal state. The shaft may be rotated by an arbitrary angle.

<D-5: Judgment of good or bad lung ventilation>
The quality of the right lung ventilation ability can be determined from the inclination angle of the locus in the Lissajous figure for the right lung. Also, the quality of the left lung ventilation ability can be determined from the inclination angle of the locus in the Lissajous figure for the left lung. In the following, the case of the Lissajous figure for the right lung will be described as an example, but the Lungs Lissajous figure for the left lung is also judged to be good or bad by the same method as that for the Lissajous figure for the right lung. It is possible.

  For example, as shown in FIG. 54, in the case of chest respiration, the CPU 170 causes the Lissajous figure for one breath for the right lung (the measured value of the third bioelectric impedance ZbR obtained at each sampling timing and the first bioelectric impedance). From the XY coordinate value determined by the measured value of ZaR), an approximate straight line LN is obtained by the least square method or the like. Next, the CPU 170 calculates an angle α formed by the approximate straight line LN and the X axis, and sets this as the inclination angle α of the locus in the Lissajous figure for the right lung.

  As shown in FIG. 54, when the X-axis is the third bioelectrical impedance ZbR and the Y-axis is the first bioelectrical impedance ZaR, an ellipse indicating the trajectory for one breath rises as the right lung ventilation capacity increases. (Inclination angle α increases and approaches 90 degrees). Conversely, as the ventilation capacity of the right lung is lower, an ellipse indicating the trajectory for one breath falls (the inclination angle α decreases and approaches 0 degrees). Therefore, the CPU 170 compares the inclination angle α with a predetermined reference inclination angle β, determines that the ventilation ability of the right lung is good when the inclination angle α is equal to or larger than the reference inclination angle β, and the inclination angle α is the reference inclination. If the angle is smaller than β, it can be determined that the right lung has poor ventilation capacity. The reference inclination angle β is a threshold value for determining the quality of the lung ventilation ability, and can be determined based on the inclination angle of the trajectory for one breath collected from a large number of subjects in advance. In addition, the value of the reference inclination angle β can basically adopt the same value for the left and right lungs and is stored in the first storage unit 120.

  As described above, the quality of the ventilation ability of the right lung can be easily determined from the locus of the Lissajous figure for the right lung. Note that the inclination angle of the trajectory for one breath varies depending on the posture at the time of measurement, such as standing, sitting, and supine. Therefore, a plurality of values of the reference inclination angle β may be stored in the first storage unit 120 in association with the posture at the time of measurement. In this case, for example, the posture at the time of measurement may be input from the input unit 150, and the value of the reference inclination angle β corresponding to the input posture may be read from the first storage unit 120 and used. Further, the reference inclination angle β stored in the first storage unit 120 is set as a standard value, and the standard value is used as the height, age, sex (step S1 in FIG. 5) input in advance, and the weight measured in advance. You may correct | amend by the calculation using (step S2 of FIG. 5) etc.

  As shown in FIG. 55, when the Lissajous figure for the right lung is rotated by the coordinate conversion process so that the straight line indicating the reference inclination angle β is vertical, an ellipse indicating the trajectory for one breath is in the vertical direction. It can be determined that the right lung has a good ventilation ability and the right lung has a poor ventilation ability when it is tilted to the left than the vertical direction. In the case of abdominal breathing as shown in FIG. 56, an approximate straight line LN is obtained for the portion surrounded by an ellipse indicated by a solid line in the locus of the Lissajous figure for one breath for the right lung. As in the case of the expression breathing, it is possible to determine whether the right lungs have good ventilation ability. In the case of draw-in breathing, the right / left ventilation ability can be determined in the same manner as in chest breathing.

  Further, the locus of the Lissajous figure used for the determination of the quality of the ventilation ability is not necessarily limited to the locus for one breath, and may be the locus for two breaths or the locus for half breaths. Moreover, even if a Lissajous figure with the X axis and Y axis swapped, or a Lissajous figure with the X axis and Y axis rotated by an arbitrary angle while maintaining an orthogonal state, the ventilation capacity is determined from the inclination angle of the trajectory. Pass / fail can be determined. Further, the value of the reference inclination angle β stored in the first storage unit 120 is set to an arbitrary value, and it is determined whether or not the ventilation capacity of the right lung or the left lung is higher than a predetermined reference capacity value. May be.

  In the fourth embodiment described above, only one of the two Lissajous figures for the right lung and the left lung may be displayed. For example, when performing a breathing exercise on the right lung, the subject can operate the input unit 150 to instruct to display only the Lissajous figure for the right lung. In this case, the CPU 170 performs each process except the steps S1105 to S1107 and S1109 in the Lissajous figure display process (FIG. 43) and displays only the Lissajous figure for the right lung. Even when only one of the Lissajous figures is displayed as described above, the above-described trajectory display process, assist display, and determination of whether the lung ventilation ability is good or not can be performed.

  In addition, the CPU 170 performs each process except the steps S790, S810, S840, and S860 in the respiration level detection process (FIGS. 22 and 23) described in the second embodiment to obtain the first relative value ΔZaR and the second relative value. A value ΔZaL, a third relative value ΔZbR, and a fourth relative value ΔZbL are calculated, and display data of a Lissajous figure for the right lung is generated using the first relative value ΔZaR and the third relative value ΔZbR, while the second relative value The display data of the Lissajous figure for the left lung may be generated using ΔZaL and the fourth relative value ΔZbL. That is, the CPU 170 generates display data of a Lissajous figure for the right lung having one axis of the two axes orthogonal to each other as the first relative value ΔZaR and the other axis as the third relative value ΔZbR. The left lung Lissajous figure display data may be generated with the second axis as the second relative value ΔZaL and the other axis as the fourth relative value ΔZbL. Also in this case, only one of the two Lissajous figures for the right lung and the left lung may be displayed.

  Moreover, this embodiment and 1st-3rd embodiment can be combined suitably. For example, the biometric apparatus 1 displays a Lissajous figure and displays the bar graphs BG1 and BG2 shown in FIG. 21, the bar graphs BG1 to BG4 shown in FIG. 27, or the bar graphs BG5 and BG6 shown in FIG. Can be displayed.

<E: Modification>
The present invention is not limited to the above-described embodiments, and for example, the following modifications are possible. Also, two or more of the modifications shown below can be combined.

(1) Modification 1
In the above-described embodiment, the CPU 170 calculates, for each breath of the subject, the sum of absolute values of the peak value ΔZaR (MAX) and the bottom value ΔZaR (MIN) of the first relative value ΔZaR in the one breath. For example, the CPU 170 extracts the right lung respiration level BR1 as the right lung respiration level BR1, but for example, the CPU 170 takes the average value of the first relative value ΔZaR and the first relative value ΔZaR in the exhalation for each breath of the subject A mode of extracting the sum of absolute values with the average value of the first right lung respiration level BR1 may be used. The same applies to the first left lung respiration level BL1, the second right lung respiration level BR2, and the second left lung respiration level BL2.

(2) Modification 2
Further, for example, the CPU 170 may obtain a difference between the first right lung respiration level BR1 and the first left lung respiration level BL1 in one respiration and display the result for each respiration of the subject. Good. Similarly, for each breath of the subject, the CPU 170 obtains a difference between the second right lung breathing level BR2 and the second left lung breathing level BL2 in one breath and displays the result. Good.

(3) Modification 3
In the first embodiment described above, the CPU 170 displays the first right lung respiration level BR1 as the first bar graph BG1, and the first left lung respiration level BL1 as the second bar graph BG2. For example, as shown in FIG. 57, the CPU 170 displays the first right lung respiration level BR1 and the first left lung respiration level BL1 as one bar graph BG0. May be. In this aspect, the number of stages on the right lung side among the number of stages of the bar graph BG0 to be displayed is determined according to the magnitude of the first right lung respiratory level BR1, while the number of stages on the left lung side is It is determined according to the magnitude of the first left lung respiration level BL1. Similarly, the second right lung respiration level BR2 and the second left lung respiration level BL2 may be displayed as one bar graph.

(4) Modification 4
In the third relative value calculation process (step S800 in FIGS. 22 and 31), the third centering value ZbR0 is obtained based on the measured value of the third bioelectrical impedance ZbR at the first zero cross timing. For example, similarly to the generation method of the first centering value ZaR0 or the second centering value ZaL0, based on the moving average processing result using the measured value of the third bioelectrical impedance ZbR at each of a predetermined number of sampling timings, The third centering value ZbR0 may be obtained. In other words, the third centering value ZbR0 may be obtained independently without being related to the first bioelectrical impedance ZaR. The same applies to the method of generating the fourth centering value ZbL0.

(5) Modification 5
In the above-described embodiment, the limb induction eight-electrode method using both hands and feet as the contact points of the electrodes has been described as an example of the current electrode and the voltage electrode, but the present invention is not limited to this. For example, the first bioelectric impedance ZaR to the fourth bioelectric impedance ZbL may be measured by directly attaching the current electrode and the voltage electrode to the trunk of the subject. Further, the bioelectrical impedance of the upper trunk may be measured in combination with the limb induction method with the ear electrode. In this case, by using the ear electrode, the measurement of the bioelectrical impedance of the upper trunk can be performed by one-arm measurement rather than by both-arm measurement. In the case where an ear electrode is used, a combination with sound notification / stimulation such as voice is effective by incorporating the ear electrode into an earphone or a headphone.
In the above-described embodiment, the measurement is performed in the standing position. However, the present invention is not limited to this, and the bioelectric impedance in the toilet seat may be measured. In this case, electrodes can be secured on the toilet seat and handrail. Furthermore, the bioelectrical impedance may be measured in a pocketable or wearable relaxation posture (chair sitting position, etc.). In this case, an electrode can be secured for a handrail such as a massage chair and a footrest.
Furthermore, respiration measurement during bathing is also possible. In this case, electrodes are provided on the bathtub handrail part, the bottom of the bathtub bottom, and the sole contact side part. Current flow becomes dominant because the trunk is made of physiological saline rather than hot water in the bathtub. Therefore, breathing training can be performed in a relaxed state during bathing.
In addition, a sphygmomanometer that is brought into contact with the sphygmomanometer arm band by hand or the like is added to the biometric device 1 of the above-described embodiment, and electrodes are arranged on the sphygmomanometer to control respiratory changes and tension of arm muscles. You may utilize as correction information at the time of blood-pressure measurement.
In addition, it is desirable that the subject can perform respiration measurement and respiration training in a relaxed state. Therefore, during breathing measurement or breathing exercise, a place where you can display a peaceful landscape image, play music with peace of mind, a cry of a bird, a sound of a waterfall, etc., or perform a breathing measurement or breathing exercise It is also important to adjust the temperature and humidity. In addition, breathing exercise training videos may be added to increase training efficiency.

(6) Modification 6
By using the bar graphs similar to the bar graphs BG1 and BG2 shown in FIG. 21, assist display for instructing the subject's breathing can be performed. For example, when it is determined that a small-sized breath is performed once and then a moderate-sized breath is performed once as a training menu for training breathing, the CPU 170 displays the target and The bar graph BG1 ′ for the right lung and the bar graph BG2 ′ for the left lung corresponding to a small-sized breath are generated and displayed on the display unit 160 as bar graphs indicating the magnitude of breathing to be performed. Before the first breath is taken after the first breath, the bar graph BG1 'for the right lung and the bar graph BG2' for the left lung corresponding to the medium-sized breath are generated and displayed. 160. In addition, if the display timing of the bar graphs BG1 ′ and BG2 ′ indicating the target breathing magnitude is controlled, the breathing rhythm of the subject can be instructed. Further, only one of the two bar graphs BG1 ′ and BG2 ′ may be displayed. For example, if breathing training is performed for the right lung, only the right lung bar graph BG1 ′ may be displayed. In addition, both the bar graphs BG1 and BG2 indicating the subject's breathing magnitude and the bar graphs BG1 'and BG2' indicating the target breathing magnitude are displayed, and the subject sets his / her breathing magnitude and target Breathing exercises may be performed while comparing the magnitude of breathing. In addition, with respect to the bar graphs BG1 to BG4 shown in FIG. 27 and the bar graphs BG5 and BG6 shown in FIG. 36, an assist display for instructing the breathing of the subject can be performed using the same bar graph.

  In addition, as shown in FIG. 58, a schematic diagram of the lungs indicating the magnitude of breathing may be displayed on the display unit 160. In this case, the area of the colored portion of the lung increases as the respiration increases, and the area of the colored portion of the lung decreases as the respiration decreases. When there is a difference in ventilation capacity between the left and right lungs, the areas of the colored portions are different between the right lung and the left lung as shown in FIG. The schematic diagram of the lung may be displayed based on the measurement result, or may be displayed as breathing instruction information. Further, instead of the schematic diagram of the lung, an animation showing the state of lung expansion or contraction may be used.

(7) Modification 7
For example, the present invention can be applied to a system using a game machine.
FIG. 59 is a diagram showing a configuration of the biometric system 5 using the home game machine 300. As shown in FIG. As shown in the figure, the biological measurement system 5 includes a biological information input device 200 ′, a game machine 300, a controller 350, and a monitor 400. In addition, the optical disk 500 is inserted into the disk slot of the game machine 300.

  The biological information input device 200 ′ includes a platform 20 ′ on which a subject is placed, a left-hand electrode unit 30 </ b> L, and a right-hand electrode unit 30 </ b> R. This biometric information input device 200 ′ has basically the same configuration as the bioelectrical impedance measuring unit 200 shown in FIG. 1, and has a configuration in which a scale is added. The biological information input device 200 ′ is connected to the controller 350 via a communication cable, measures the bioelectrical impedance and body weight of each part of the subject, and supplies the biological information to the game machine 300 via the controller 350. To do.

  The controller 350 is an input device for inputting operation information and the like. The controller 350 communicates with the game machine 300 by wireless communication such as Bluetooth (registered trademark), and transmits operation information input by the subject and biometric information output from the biometric information input device 200 ′ to the game machine 300. For example, information such as height, age, and sex can be input by operating the controller 350. The monitor 400 is, for example, a television receiver, and is connected to the game machine 300 via a communication cable. The optical disc 500 stores programs and data for controlling various processes described in the first to fourth embodiments and the modifications (1) to (6).

  In the figure, the case where the biological information measured by the biological information input device 200 ′ is supplied to the game machine 300 via the controller 350 is illustrated, but the biological information input device 200 ′ stores the biological information. You may supply directly to the game machine 300 by wireless communication. In this case, the biometric information input device 200 ′ includes a wireless communication module for performing wireless communication with the game machine 300. Further, the biometric information input device 200 ′ may directly supply the biometric information to the game machine 300 through wired communication. In this case, the biological information input device 200 ′ and the game machine 300 may be directly connected with a communication cable. Further, a left-hand controller 350 provided with a current electrode X3 and a voltage electrode Y3 is provided instead of the left-hand electrode portion 30L, while a current electrode X4 and a voltage electrode Y4 are provided instead of the right-hand electrode portion 30R. Alternatively, a right hand controller 350 may be provided.

FIG. 60 is a block diagram showing a configuration of the game machine 300.
As shown in the figure, the game machine 300 includes a ROM 301, a RAM 302, a hard disk 303, a disk drive 310, a wireless communication module 320, an image processing unit 330, an audio processing unit 340, and a CPU 360. The ROM 301 stores a program that performs basic control of the game machine 300. The RAM 302 is used as a work area for the CPU 360. The hard disk 303 stores programs and data read from the optical disc 500 such as a training menu management table TBL (FIG. 61) described later. The disk drive 310 reads programs and data from the optical disk 500. The program and data are not only provided to the game machine 300 by a recording medium such as the optical disc 500, but may be downloaded from a server or the like via a communication network. In this case, the game machine 300 includes a network communication module.

  The wireless communication module 320 controls wireless communication performed with the controller 350. The wireless communication module 320 is an input unit for inputting the biological information measured by the biological information input device 200 ′ to the game machine 300. The image processing unit 330 generates image data and outputs it to the monitor 400. The audio processing unit 340 generates audio data such as sound effects and audio and outputs the audio data to the monitor 400 (speaker). The CPU 360 controls the entire game machine 300 by executing various programs stored in the ROM 301, the hard disk 303, and the like. For example, the CPU 360 can control the wireless communication module 320 and communicate with the biological information input device 200 ′ via the controller 350. Further, the CPU 360 can instruct the biological information input device 200 'to switch the current electrodes X1 to X4 and the voltage electrodes Y1 to Y4, measure the bioelectrical impedance, measure the weight, and the like.

  Further, the CPU 360 performs, for example, the respiration detection process and the respiration level display process described in the first embodiment, and indicates the first bar graph BG1 indicating the ventilation capacity of the upper part of the right lung and the ventilation capacity of the upper part of the left lung. The second bar graph BG2 can be displayed on the monitor 400 (FIG. 21). Further, the CPU 360 performs the respiration detection process and the respiration level display process described in the second embodiment, and in addition to the first bar graph BG1 and the second bar graph BG2, the third bar indicating the ventilation ability of the middle lower part of the right lung. A graph BG3 and a fourth bar graph BG4 indicating the ventilation capacity of the middle lower part of the left lung can be displayed on the monitor 400 (FIG. 27). In addition, the CPU 360 performs the respiration detection process and the respiration level display process described in the third embodiment, the fifth bar graph BG5 indicating the magnitudes of chest respiration and abdominal respiration on the right side of the trunk, and the left side of the trunk. A sixth bar graph BG6 indicating the magnitude of each of the chest breathing and the abdominal breathing can be displayed on the monitor 400 (FIG. 36). Further, the CPU 360 can perform the Lissajous figure display processing described in the fourth embodiment and display the Lissajous figure for the right lung and the left lung on the monitor 400. Further, the CPU 360 can perform processing for training the subject's breathing using a bar graph, a Lissajous figure, a schematic diagram of the lung, and the like. As described above, the CPU 360 can perform various processes described in the first to fourth embodiments and the modifications (1) to (6).

FIG. 61 is a diagram showing a data configuration of the training menu management table TBL.
The training menu management table TBL is used for allowing the subject to perform breathing training using a training menu suitable for his / her breathing ability. The training menu management table TBL has a training menu for training breathing and a clear condition for clearing this class and proceeding to the next class for each class (rank) determined according to the breathing ability. It is remembered. For example, in the example shown in the figure, five classes from rank 1 to rank 5 are provided. In addition, 20 training menus are prepared for each class.

  For example, as a specific example of the training menu, training to master chest breathing and abdominal breathing, training to master full breathing that combines chest breathing and abdominal breathing, training to master draw-in breathing, Using exercises to increase the ventilation capacity of the lungs by abdominal breathing and complete breathing, training to increase the ventilation capacity of the left and right lungs, training to increase respiratory function and motor function by draw-in breathing, various poses used in yoga etc. The exercise | movement which reinforces a respiratory function and an exercise | movement function by performing various respiration while giving a load to a respiratory muscle can be illustrated.

  Complete breathing is a breathing method that uses the abdomen, chest, and shoulders to make the best use of the ventilation capacity of the lungs and exhale and inhale. For complete breathing, for example, when inhaling, first inhale while inflating the belly, then inhale while expanding the ribcage with the feeling of protruding the chest forward, and finally inhale while raising the shoulder. As a result, the diaphragm is fully opened. When exhaling, on the contrary, first exhale while lowering the shoulder, then exhale while returning the expanded rib cage, and finally exhale while denting the abdomen.

  The training menu uses, for example, a Lissajous figure showing the subject's breathing state (or a bar graph showing the subject's breathing state or a schematic diagram of the lungs), while the subject confirms his / her breathing state. Use the Lissajous figure that shows the state of the target breathing (or the bar graph and the schematic diagram of the lungs that show the target breathing state), and the subject confirms the target breathing state. A Lissajous figure that shows the subject's breathing state (or a bar graph or a schematic diagram of the lungs that shows the subject's breathing state) and a Lissajous figure that shows the target breathing state (or Using both the bar graph showing the target breathing and the schematic diagram of the lungs, the subject can train while comparing his / her breathing with the target breathing It is included, such as those in.

  As specific examples of the clear condition, for example, the right lung respiration level (first right lung respiration level BR1, second right lung respiration level BR2) or left lung inhalation level (first left lung respiration level BL1, second 2) Left lung respiration level BL2) is equal to or higher than a predetermined reference value, the magnitude of chest or abdominal respiration for each lung is equal to or higher than a predetermined reference value, 20 exercises For example, it is possible to exemplify that all menus have been trained. In the training menu management table TBL, the number of classes may be two or more, and the training menu may be one or more for each class. Moreover, the following can be illustrated as a specific example of classification and training content.

[Rank 1 / Training for patients with moderate to advanced respiratory disease]
Rehabilitation training to train the chest respiratory muscles that perform basic thoracic breathing exercises by thoracic breathing to restore respiratory function that has been reduced by respiratory disease.
[Rank 2: Training for patients with mild respiratory disease]
Rehabilitation training for abdominal respiratory muscles such as the diaphragm to be trained by abdominal breathing to restore respiratory function that has been reduced by respiratory disease.
[Rank 3 / Standard training for healthy people]
Complete breathing combined with chest breathing and abdominal breathing to train both chest and abdominal breathing muscles to further improve respiratory function and reduce respiratory function due to smoking, lifestyle-related diseases, lack of exercise, aging, etc. Training to improve.
[Rank 4 / light load training]
Training to strengthen the inner muscles of the trunk (such as transverse abdominal muscles and standing spine muscles) by draw-in breathing, improve respiratory function, and prevent back pain and exercise function.
[Rank 5 / Medium-level load training for athletes]
Training for strengthening motor functions by combining postures that apply stress to respiratory muscles, such as those used in yoga, and draw-in breathing.

  In addition, the training for patients with respiratory diseases listed as ranks 1 and 2 is based on the premise that the medical guidance at the treatment facility is strictly followed. Depending on the level of the disease, the subject is basically a person whose diaphragm functions to some extent and who can expect improvement in respiratory function by training breathing. Moreover, it is possible to combine loads such as breathing while purging the mouth with respect to ranks 1 to 5. In addition, the combination of breathing method and pose, the time distribution of training, and the like can be arbitrarily determined as appropriate.

FIG. 62 is a flowchart showing the processing contents of the breathing exercise management process.
The breathing training management process shown in the figure is executed by the CPU 360 when, for example, the subject starts breathing training using the system 5. When starting the respiratory training management process, the CPU 360 first performs a process of detecting the breathing ability of the subject (step S1201). For example, the CPU 360 notifies a message instructing the subject to perform chest-type breathing or abdominal-type breathing, and performs the breath detection process, the breath level display process, or the first described in any of the first to third embodiments. The quality of the Lissajous figure display process and lung ventilation ability described in the fourth embodiment is determined. Thus, the CPU 360, for example, the right lung ventilation capacity (upper right and lower middle ventilation capacity), the left lung ventilation capacity (upper left and upper middle ventilation capacity), the chest type for each lung The magnitude of breathing or abdominal breathing is detected as the subject's breathing ability.

  Note that, in order to detect the breathing ability of the subject from normal breathing, the process shown in step S1201 may be performed without notifying the subject that the breathing is being measured. In step S1201, the first bioelectrical impedance ZaR and the second bioelectrical impedance ZaL may be measured to detect the breathing ability of the subject, or the third bioelectrical impedance ZbR and the fourth bioelectrical impedance ZbL may be detected. The measurement may be performed to detect the breathing ability of the subject, or the first to fourth bioelectric impedances ZaR, ZaL, ZbR, and ZbL may be measured to detect the breathing ability of the subject.

  Next, the CPU 360 refers to the training menu management table TBL, and identifies a class corresponding to the subject's breathing ability detected in step S1201 (step S1202). Further, the CPU 360 selects a training menu corresponding to the identified class from the training menu management table TBL (step S1203). For example, when the class of the subject is rank 3, the CPU 360 refers to the training menu management table TBL shown in FIG. 61 and selects the menus 41 to 60. If there is a difference in ventilation capacity between the left and right lungs, different training menus may be selected for the left and right lungs.

  Thereafter, the CPU 360 performs a process for training the subject's breathing using the training menu selected in step S1203 (step S1204). For example, when the class of the subject is rank 3, the CPU 360 performs a process for training breathing using the menus 41 to 60. In addition, when rank 3 is the above-described standard training for healthy persons, the CPU 360 performs training for mastering complete breathing that combines chest breathing and abdominal breathing based on the training menu, and lungs through complete breathing. Provide training to increase the ventilation capacity of children. Further, the CPU 360 displays, for example, a Lissajous figure (or a bar graph or a schematic diagram of the lungs indicating the breathing state of the subject) on the monitor 400, and confirms the breathing state of the subject. While being able to train. In addition, the CPU 360 displays a Lissajous figure indicating the target breathing state (or a bar graph or a schematic diagram of the lungs indicating the target breathing state) on the monitor 400 to confirm the subject's target breathing state. While being able to train. In addition, the CPU 360 displays a Lissajous figure (or a bar graph or a schematic diagram of the lungs indicating the state of breathing of the subject) and a Lissajous figure (or a target breathing state) indicating the state of the target breathing. Both a bar graph indicating the state and a schematic diagram of the lung) can be displayed on the monitor 400 so that the subject can perform training while comparing his / her breathing state with the target breathing state.

  Thereafter, the CPU 360 reads the clear condition corresponding to the current class of the subject from the training menu management table TBL, and determines whether or not the clear condition is satisfied (step S1205). For example, when the current class of the subject is rank 3, the CPU 360 reads the condition C from the training menu management table TBL shown in FIG. 61 and determines whether or not the condition C is satisfied.

  For example, when the condition C is “the ventilation capacity of the right lung and the ventilation capacity of the left lung are both equal to or higher than a predetermined reference value”, the CPU 360 performs the breathing described in any of the first to third embodiments. A detection process and a respiration level display process are performed, and it is determined whether or not the ventilation capacity of the right lung and the ventilation capacity of the left lung are both equal to or higher than a reference value. Further, when the condition C is “finished all 20 training menus”, the CPU 360 determines that the clear condition is satisfied when all the trainings from the menus 41 to 60 have been completed.

  If the result of step S1205 is negative, the process returns to step S1204, and breathing training in the current class is continued. On the other hand, if the result of step S1205 is affirmative, the CPU 360 ranks up the subject's class to the next class (step S1206), and then returns to step S1203. For example, when the class of the subject is rank 3, the CPU 360 changes the class of the subject to rank 4 in step S1206 and returns to step S1203. Thereby, a training menu (menu 61 to menu 80) corresponding to rank 4 is selected from the training menu management table TBL, and a new training is started.

  Note that when the subject operates the controller 350 to instruct the end of exercise, the breathing exercise management process shown in FIG. At this time, the CPU 360 stores rank information indicating the current class of the subject in the hard disk 303, and when the subject performs breathing training next time, the rank information stored in the hard disk 303 is read and processed from step S1203. To start.

  As described above, according to this modification, by using the game machine 300, it is possible to easily measure respiration in the home in the same way as measuring body weight and body fat. In addition, breathing training can be done easily at home. Further, according to the present modification, the subject can perform respiration training based on the training menu corresponding to his / her respiration ability, so that respiration can be efficiently trained. In addition, the training menu is prepared for each class, and by having the game characteristics of proceeding to the next class while clearing each class, it is possible to perform breathing training while having fun, so subjects for breathing training You can also increase your motivation.

  In addition, you may perform a breathing exercise management process (FIG. 62) in the biometric apparatus 1 demonstrated by 1st-4th embodiment. In this case, a program for performing a breathing exercise management process, a breathing exercise management table TBL (FIG. 61), and the like may be stored in the first storage unit 120. Further, instead of the game machine 300, a personal computer or a portable electronic device (for example, a mobile phone) may be used. In the case of a portable electronic device, a head mounted display may be used as a display device. .

(8) Modification 8
The biometric device 1 may not include the display unit 160 and may display a Lissajous figure, a bar graph, or the like on an external display device. The biometric apparatus 1 does not include the bioelectrical impedance measuring unit 200 but includes an input unit that inputs the bioelectrical impedance of the trunk measured by the external bioelectrical impedance measuring apparatus by wireless communication or wired communication. Also good. In this case, the input unit is, for example, a communication interface such as a wireless communication module, a network communication module, or a USB (Universal Serial Bus) interface.

(9) Modification 9
The Lissajous figure may be displayed not only when breathing training is performed, but also when breathing is measured (when a breathing level indicating lung ventilation capacity is measured). The present invention is not limited to an apparatus or system having only a respiration measurement function or a respiration training function. For example, the present invention can be applied to various training apparatuses and training systems in which a breath measurement function and a breath training function are incorporated in a part thereof, such as a fitness training apparatus.

(10) Modification 10
If the biometric apparatus 1 described in the third embodiment is applied, whether the breathing on the right side of the subject's trunk is a draw-in breath or whether the breathing on the left side of the subject's trunk is a draw-in breath Can be determined. Hereinafter, the case where the determination of the draw-in breath is performed for each of the left and right trunks will be described by taking the right side of the trunk as an example. Since the hardware configuration of the biometric apparatus is basically the same as that described in the first embodiment, the same reference numerals as those in the first embodiment are used and description thereof is omitted.

  In the case of draw-in respiration, as shown in FIG. 41, the bioelectrical impedance Za of the upper trunk and the bioelectrical impedance Zb of the middle trunk both change in the increase direction during inspiration and decrease in the expiration period. This change is the same as for chest breathing. This is because in the case of draw-in breathing, exhalation and inhalation are performed by chest breathing while maintaining a state where the abdomen is recessed. However, in the case of draw-in respiration, since force is applied to the abdomen to dent the abdomen, the amplitude reference level of the bioelectrical impedance Zb in the middle of the trunk is higher than in the case of chest respiration. As described above, the amplitude reference level of the bioelectrical impedance Zb in the middle of the trunk is different between the case of the draw-in respiration and the case of the chest respiration, and it is possible to determine the draw-in respiration using this. That is, in the case of the right side of the trunk, the average value of ΔRib / ΔAb exceeds 1.0 after the ΔRib / ΔAb estimation calculation process (FIGS. 33 and 34) described in the third embodiment is performed. In the case of discriminating the chest breathing, the amplitude reference level (third centering value ZbR0) of the third bioelectrical impedance ZbR is a predetermined value higher than the amplitude reference level of the third bioelectrical impedance ZbR in the case of chest breathing. If it is higher than this, this may be determined as draw-in respiration.

  However, the amplitude reference level of the third bioelectrical impedance ZbR in the case of thoracic breathing differs for each subject. Therefore, in order to determine draw-in respiration by the method described above, it is necessary to measure in advance the amplitude reference level of the third bioelectrical impedance ZbR in the case of chest respiration and store it in the second storage unit 130. . In addition, the above-described predetermined value needs to be stored in the first storage unit 120 in advance.

  For this reason, the biometric apparatus 1 (CPU 170) according to this modification, for example, reports a message instructing the subject to perform chest-type breathing, and obtains a number of items acquired during the period in which the subject is performing chest-type breathing. An average value of the third centering value ZbR0 is calculated and stored in the second storage unit 130 as the amplitude reference level of the third bioelectrical impedance ZbR in the case of chest breathing. Hereinafter, the amplitude reference level of the third bioelectrical impedance ZbR in the case of thoracic breathing stored in the second storage unit 130 in this way is denoted as ZbR1. On the other hand, the predetermined values stored in the first storage unit 120 are the amplitude reference level of the third bioelectrical impedance ZbR in the case of chest respiration and the third living body in the case of draw-in respiration collected from a large number of subjects in advance. The value can be set based on the difference between the electrical impedance ZbR and the amplitude reference level. Hereinafter, the predetermined value stored in the first storage unit 120 is expressed as ΔZbR1.

FIG. 63 is a flowchart showing the processing content of the breathing type determination processing (for trunk right side).
The processing shown in the figure is executed after performing the ΔRib / ΔAb estimation calculation processing (FIGS. 33 and 34) on the right side of the trunk described in the third embodiment. When the CPU 170 starts the respiration type determination process, first, it is determined whether or not the average value ([ΣΔRib / ΔAb] / Ni) of ΔRib / ΔAb obtained by the ΔRib / ΔAb estimation calculation process is 1.0 or less. (Step S1301). If the result of step S1301 is affirmative, the CPU 170 determines that the breathing on the right side of the subject's trunk is abdominal breathing (step S1302).

  On the other hand, if the result of step S1301 is negative, the CPU 170 reads the amplitude reference level ZbR1 of the third bioelectrical impedance ZbR in the case of chest breathing from the second storage unit 130, and also stores the predetermined value ΔZbR1 in the first storage unit. Read from 120 (step S1303). Note that the predetermined value ΔZbR1 stored in the first storage unit 120 is set as a standard value, and this standard value is used for the height, age, sex (step S1 in FIG. 5) input in advance, and the weight ( You may correct | amend by the calculation using step S2) of FIG.

  Thereafter, the CPU 170 acquires the third centering value ZbR0 generated in the process of calculating the third relative value ΔZbR in step S800 of the respiration level calculation process (FIGS. 31 and 32) described in the third embodiment. Then, the CPU 170 determines whether or not the third centering value ZbR0 is greater than or equal to the sum of the amplitude reference level ZbR1 of the third bioelectrical impedance ZbR and the predetermined value ΔZbR1 in the case of chest breathing (step S1304). . Note that the third centering value ZbR0 used in step S1304 may be, for example, the average value of the third centering value ZbR0 in the immediately preceding one breath or the average value of the third centering value ZbR0 in the immediately preceding plural sampling periods. Good. If the result of step S1304 is affirmative, the CPU 170 determines that respiration on the right side of the subject's trunk is draw-in respiration (step S1305). On the other hand, if the result of step S1304 is negative, the CPU 170 determines that breathing on the right side of the subject's trunk is chest-type breathing (step S1306).

  Note that ZbR1 (the amplitude reference level of the third bioelectrical impedance ZbR in the case of chest breathing) stored in the second storage unit 130 is a plurality of third numbers acquired during the period in which the subject is performing chest breathing. It is not limited to the average value of the centering value ZbR0. For example, it may be one third centering value ZbR0 acquired at an arbitrary timing during a period in which the subject is performing chest breathing. In addition, the CPU 170 does not add a predetermined value ΔZbR1 to ZbR1 read from the second storage unit 130, but multiplies ZbR1 by a predetermined coefficient (for example, 1.035) larger than 1.0 to add the value (ZbR1 + ΔZbR1). A threshold value corresponding to may be calculated. As in the case of the predetermined value ΔZbR1, the coefficient in this case is also the amplitude reference level of the third bioelectrical impedance ZbR collected from a large number of subjects in advance and the third bioelectric in the case of draw-in respiration. The value can be set based on the difference between the impedance ZbR and the amplitude reference level. Further, the threshold value calculated in this way is stored in the second storage unit 130 instead of ZbR1, and the third centering value ZbR0 is read from the second storage unit 130 in step S1304 of the above-described respiration type determination process. It may be determined whether or not it is equal to or greater than the threshold value.

  According to the above configuration, it is possible to accurately determine in real time whether or not respiration on the right side of the subject's trunk is draw-in respiration. In addition to draw-in breathing, it is also possible to determine whether breathing on the subject's trunk right side is abdominal breathing or chest breathing. By using the same method as in the case of the right side of the trunk, it is possible to determine whether the breathing on the left side of the subject's trunk is a draw-in breath or whether it is an abdominal breathing or a chest breathing. .

Moreover, the biometric apparatus 1 may determine draw-in respiration for each left and right trunk by the method described below.
[Method 1] As shown in FIG. 41, in the case of draw-in respiration, only the amplitude reference level of the bioelectrical impedance Zb in the middle of the trunk is shifted upward in comparison with the case of chest respiration or abdominal respiration. Therefore, in the case of the right side of the trunk, the CPU 170 has a first centering value ZaR0 indicating the amplitude reference level of the first bioelectrical impedance ZaR and a third centering value ZbR0 indicating the amplitude reference level of the third bioelectrical impedance ZbR. When only the third centering value ZbR0 increases by a predetermined value (for example, 0.5Ω) or more, it is determined that it is a draw-in respiration. In the case of the left side of the trunk, the CPU 170 has a second centering value ZaL0 indicating the amplitude reference level of the second bioelectrical impedance ZaL and a fourth centering value ZbL0 indicating the amplitude reference level of the fourth bioelectrical impedance ZbL. When only the fourth centering value ZbL0 increases by a predetermined value (for example, 0.5Ω) or more, it is determined that it is a draw-in respiration.

[Method 2] As shown in FIG. 41, in the case of draw-in respiration, the amplitude value (maximum value-minimum value) of the bioelectrical impedance Za of the upper trunk and the trunk are compared with those in the case of chest respiration or abdominal respiration. Both the amplitude values (maximum value−minimum value) of the bioelectric impedance Zb in the middle part are reduced. Therefore, in order to be able to determine whether or not it is a draw-in breath from these amplitude values, a threshold value is determined for the amplitude value and stored in the first storage unit 120. In the case of the right side of the trunk, the CPU 170 monitors the amplitude value of the first bioelectrical impedance ZaR and the amplitude value of the third bioelectrical impedance ZbR, and both amplitude values are threshold values (for example, 1.. 8Ω) or less, and when only the third centering value ZbR0 is increased by a predetermined value or more by the above-described [Method 1], it is determined that the breath is a draw-in breath. Further, in the case of the left side of the trunk, the CPU 170 monitors the amplitude value of the second bioelectrical impedance ZaL and the amplitude value of the fourth bioelectrical impedance ZbL, and both amplitude values are threshold values (for example, 1.. 8Ω) or less, and when only the fourth centering value ZbL0 is increased by a predetermined value or more by the above-described [Method 1], it is determined that the breath is a draw-in breath.

[Method 3] In the case of draw-in respiration, the measurement waveform of the bioelectrical impedance Za in the upper trunk and the measurement waveform of the bioelectrical impedance Zb in the middle trunk show the same characteristics as in the case of chest respiration. That is, the bioelectrical impedance Za of the upper trunk and the bioelectrical impedance Zb of the middle trunk both change in the inspiration and change in the decrease in the expiration. Therefore, the CPU 170 monitors the measurement waveform of the first bioelectrical impedance ZaR and the measurement waveform of the third bioelectrical impedance ZbR in the case of the right side of the trunk. When the same characteristic is exhibited and only the third centering value ZbR0 is increased by a predetermined value or more by the above-described [Method 1], it is determined as the draw-in respiration. Further, the CPU 170 monitors the measurement waveform of the second bioelectrical impedance ZaL and the measurement waveform of the fourth bioelectrical impedance ZbL in the case of the left side of the trunk. When only the fourth centering value ZbL0 is increased by a predetermined value or more by [Method 1] described above, it is determined that the breathing is a draw-in breath.

1 Biological Measuring Device 5 Biological Measuring System 120 First Storage Unit 150 Input Unit 170 CPU
200 Bioelectrical impedance measuring unit 200 ′ Biological information input device ZaR First bioelectrical impedance (right upper trunk)
ZaL 2nd bioelectric impedance (upper trunk left side)
ZbR 3rd bioelectric impedance (right side of the trunk)
ZbL 4th bioelectric impedance (left side of mid-trunk)
300 game machine 320 wireless communication module 360 CPU
400 monitors

Claims (27)

A bioelectrical impedance measuring unit that measures bioelectrical impedance for a part including the right lung of the subject and a part including the left lung;
Based on the measurement value of the bioelectrical impedance of the part including the right lung, while obtaining the right lung respiration level indicating the ventilation ability of the right lung, while based on the measurement value of the bioelectrical impedance of the part including the left lung, A respiratory level calculation unit for obtaining a left lung respiratory level indicating the ventilation capacity of the left lung,
A respiratory level measuring device characterized by that. The bioelectrical impedance measuring unit is
A first bioelectrical impedance on the right side of the upper trunk that includes the upper part of the subject's right lung and does not include the abdomen, and a second biological body on the left side of the upper trunk that includes the upper part of the left lung of the subject and does not include the abdomen Measure electrical impedance and
The respiration level calculation unit
Based on the measurement value of the first bioelectrical impedance, a first right lung respiration level indicating the ventilation capacity of the upper part of the right lung is obtained, and on the other hand, based on the measurement value of the second bioelectrical impedance, the left lung Determining a first left lung respiratory level indicative of the upper ventilation capacity of
The respiratory level measuring device according to claim 1, wherein A first centering value generator for generating a first centering value indicating an amplitude reference level of the measurement value of the first bioelectrical impedance and a second centering value indicating the amplitude reference level of the measurement value of the second bioelectrical impedance. When,
A first relative value calculation unit for obtaining a first relative value that is a relative value of the measured value of the first bioelectrical impedance with respect to the first centering value;
A second relative value calculation unit that obtains a second relative value that is a relative value of the measurement value of the second bioelectrical impedance with respect to the second centering value;
The respiration level calculation unit obtains the first right lung respiration level based on the first relative value, and obtains the first left lung respiration level based on the second relative value.
The respiratory level measuring device according to claim 2, wherein The respiration level calculation unit calculates, for each respiration of the subject, the sum of absolute values of the maximum value and the minimum value of the first relative value in the respiration as the first right lung respiration level. Calculating a sum of absolute values of the maximum value and the minimum value of the second relative value in the one breath as the first left lung respiration level.
The respiration level measuring apparatus according to claim 3, wherein: The bioelectrical impedance measuring unit is
Measuring the first bioelectrical impedance and the second bioelectrical impedance each time the sampling timing is reached at a predetermined period;
The first centering value generator is
The first centering value is generated based on the measured value of the first bioelectrical impedance at each of the predetermined number of sampling timings, while the first centering value is generated based on the measured value of the second bioelectrical impedance at each sampling timing. 2 generate centering values,
The respiration level measuring apparatus according to claim 3 or 4, wherein The first centering value generator is
For each of the sampling timings, the measurement of the first bioelectrical impedance at each of the plurality of sampling timings within a centering period starting from a time point a predetermined time before the sampling timing and ending at the sampling timing A moving average process is performed using the value, and based on the result, the first centering value at the sampling timing is generated, while the second bioelectric impedance at each of the plurality of sampling timings within the centering period is generated. A moving average process is performed using the measurement value, and the second centering value at the sampling timing is generated based on the result.
The respiratory level measuring device according to claim 5, wherein The time length of the centering period is variably set according to the breathing rate of the subject.
The respiration level measuring device according to claim 6 characterized by things. The bioelectrical impedance measuring unit is
Each time the sampling timing is reached, the third bioelectrical impedance on the right side of the trunk including the middle lower part and the abdomen of the subject's right lung, and the middle trunk including the middle lower part and the abdomen of the subject's left lung Measure the 4th bioelectrical impedance on the left side,
A second centering value generating unit that generates a third centering value indicating an amplitude reference level of the measurement value of the third bioelectrical impedance and a fourth centering value indicating the amplitude reference level of the measurement value of the fourth bioelectrical impedance. When,
A third relative value calculation unit for obtaining a third relative value that is a relative value of the measured value of the third bioelectrical impedance with respect to the third centering value;
A fourth relative value calculation unit for obtaining a fourth relative value that is a relative value of the measurement value of the fourth bioelectrical impedance with respect to the fourth centering value;
A first zero cross timing at which the measured value of the first bioelectrical impedance is equal to the first centering value, and a second zero cross timing at which the measured value of the second bioelectrical impedance is equal to the second centering value. A zero cross timing extraction unit for extracting,
The second centering value generator is
The third centering value is generated based on the measured value of the third bioelectrical impedance at the first zero cross timing, while the fourth centering is generated based on the measured value of the fourth bioelectrical impedance at the second zero cross timing. Generate a value,
The respiration level calculation unit
Based on the third relative value, a second right lung respiratory level indicating the ventilation ability of the middle lower part of the right lung is obtained, and on the other hand, the ventilation ability of the middle lower part of the left lung is obtained based on the fourth relative value. Determining a second left lung respiratory level to indicate,
The respiration level measuring apparatus according to any one of claims 5 to 7, wherein The second centering value generator is
At each sampling timing, it is determined whether or not the sampling timing is the first zero cross timing. When the sampling timing is the first zero cross timing, the measurement of the third bioelectrical impedance at the sampling timing is performed. Based on the value, the third centering value at the sampling timing is generated. On the other hand, if the sampling timing is not the first zero cross timing, the third centering value generated at the sampling timing immediately before the sampling timing is generated. Adopted as the third centering value at the sampling timing,
The respiration level measuring apparatus according to claim 8, wherein The second centering value generator is
For each sampling timing, it is determined whether the sampling timing is the second zero cross timing. If the sampling timing is the second zero cross timing, the measurement of the fourth bioelectrical impedance at the sampling timing is performed. Based on the value, the fourth centering value at the sampling timing is generated. On the other hand, when the sampling timing is not the second zero cross timing, the fourth centering value generated at the sampling timing immediately before the sampling timing is generated. , Adopted as the fourth centering value at the sampling timing,
The respiratory level measuring device according to claim 8 or 9, wherein The respiration level calculation unit calculates, for each respiration of the subject, a sum of absolute values of the maximum value and the minimum value of the third relative value in the respiration as the second right lung respiration level. Calculating a sum of absolute values of the maximum value and the minimum value of the fourth relative value in the one respiration as the second left lung respiration level;
The respiration level measuring apparatus according to any one of claims 8 to 10, wherein The bioelectrical impedance measuring unit is
A third bioelectric impedance on the right side of the middle trunk including the middle lower part and the abdomen of the subject's right lung, and a fourth bioelectric impedance on the left side of the middle trunk including the middle lower part and the abdomen of the subject's left lung. Measure and
The respiration level calculation unit
Based on the measured value of the third bioelectrical impedance, a second right lung respiration level indicating the ventilation ability of the middle and lower part of the right lung is obtained, while on the basis of the measured value of the fourth bioelectrical impedance, the left Determining a second left lung respiratory level indicative of the ability to ventilate the lower and middle lungs;
The respiratory level measuring device according to claim 1, wherein The bioelectrical impedance measuring unit is
A first bioelectrical impedance on the right side of the upper trunk that includes the upper part of the subject's right lung and does not include the abdomen; a second bioelectrical impedance on the left side of the upper part of the trunk that includes the upper part of the left lung of the subject and does not include the abdomen; Measuring the third bioelectrical impedance on the right side of the middle trunk including the middle lower part and the abdomen of the subject's right lung and the fourth bioelectrical impedance on the left side of the middle part of the trunk including the middle lower part and the abdomen of the subject's left lung; ,
The respiration level calculation unit
Based on the measured value of the first bioelectrical impedance and the measured value of the third bioelectrical impedance, the right lung respiration level indicating the ventilation capacity of the right lung is obtained, while the measured value of the second bioelectrical impedance and the Based on the measurement value of the fourth bioelectrical impedance, a left lung respiration level indicating the ventilation capacity of the left lung is obtained.
The respiratory level measuring device according to claim 1, wherein Of the two axes orthogonal to each other, one axis is the first bioelectrical impedance and the other axis is the third bioelectrical impedance. The measured value of the first bioelectrical impedance and the measured value of the third bioelectrical impedance Display data of a first Lissajous figure showing a change over time of the second bioelectrical impedance, the one axis as the second bioelectrical impedance, and the other axis as the fourth bioelectrical impedance, A display data generating unit that generates display data of a second Lissajous figure indicating a change over time of the measurement value and the measurement value of the fourth bioelectrical impedance;
The respiration level measuring apparatus according to claim 13. The display data generation unit generates display data of the first Lissajous figure and display data of the second Lissajous figure so that the first Lissajous figure and the second Lissajous figure are displayed in an overlapping manner.
The respiratory level measuring apparatus according to claim 14, wherein The display data generation unit generates display data of the first Lissajous figure and display data of the second Lissajous figure so that a display mode of the locus of the first Lissajous figure is different from that of the second Lissajous figure. To
The respiration level measuring apparatus according to claim 14 or 15, wherein A trajectory analysis unit for detecting a difference between the trajectory of the first Lissajous figure and the trajectory of the second Lissajous figure;
The display data generation unit generates display data of the first Lissajous figure and display data of the second Lissajous figure so that the difference is highlighted and displayed;
The respiration level measuring apparatus according to any one of claims 14 to 16, wherein The first amplitude value indicating the amplitude of the measurement value of the first bioelectrical impedance, the second amplitude value indicating the amplitude of the measurement value of the second bioelectrical impedance, and the amplitude of the measurement value of the third bioelectrical impedance. An amplitude value specifying unit that specifies a third amplitude value to be displayed and a fourth amplitude value indicating the amplitude of the measurement value of the fourth bioelectrical impedance;
The display data generation unit adjusts the range of the one axis using the first amplitude value and the second amplitude value, while the other axis uses the third amplitude value and the fourth amplitude value. And generating display data for the first Lissajous figure and display data for the second Lissajous figure.
The respiratory level measuring device according to any one of claims 14 to 17, wherein The first amplitude value indicating the amplitude of the measurement value of the first bioelectrical impedance, the second amplitude value indicating the amplitude of the measurement value of the second bioelectrical impedance, and the amplitude of the measurement value of the third bioelectrical impedance. An amplitude value specifying unit that specifies a third amplitude value to be displayed and a fourth amplitude value indicating the amplitude of the measurement value of the fourth bioelectrical impedance;
The display data generation unit uses the first amplitude value and the second amplitude value as processing to generate display data for the first Lissajous figure and display data for the second Lissajous figure. A first range adjustment process for adjusting the range of the axis, and a second range adjustment process for adjusting the range of the other axis using the third amplitude value and the fourth amplitude value,
The frequency of performing the second range adjustment process is less than the frequency of performing the first range adjustment process.
The respiratory level measuring device according to any one of claims 14 to 17, wherein Of the two axes orthogonal to each other, one axis is the first bioelectrical impedance and the other axis is the third bioelectrical impedance. The measured value of the first bioelectrical impedance and the measured value of the third bioelectrical impedance Display data of a Lissajous figure indicating a change over time, or the one axis is the second bioelectrical impedance and the other axis is the fourth bioelectrical impedance, and the measured value of the second bioelectrical impedance and the A display data generating unit that generates display data of a Lissajous figure indicating a change with time of the measurement value of the fourth bioelectrical impedance;
The respiration level measuring apparatus according to claim 13. The display data generation unit generates the display data of the Lissajous figure so that the display mode of the locus of the Lissajous figure is different between the latest one breath and the other past breaths.
The respiration level measuring apparatus according to claim 20, wherein The display data generation unit generates display data of the Lissajous figure so that a display mode of a locus of the Lissajous figure changes according to an elapsed time;
The respiration level measuring apparatus according to claim 20, wherein The display data generation unit generates display data of the Lissajous figure, and generates display data of a Lissajous figure for breathing guidance according to a target breathing type and the magnitude of the breathing.
The respiration level measuring apparatus according to any one of claims 20 to 22, wherein An inclination angle calculation unit for calculating an inclination angle of the locus of the Lissajous figure;
A ventilation capability determination unit that compares the inclination angle calculated by the inclination angle calculation unit with a predetermined reference inclination angle to determine the quality of the lung ventilation capability;
The respiratory level measuring device according to any one of claims 20 to 23, wherein: A storage unit that stores a training menu for training breathing and a clear condition for clearing the class for each class determined according to the ability of breathing,
Based on the measurement result of the bioelectrical impedance measurement unit or the calculation result of the respiration level calculation unit, a respiration capability detection unit that detects the respiration capability of the subject,
Referring to the storage unit, a class corresponding to the breathing ability detected by the breathing ability detection unit is specified, and a process for training breathing of the subject is performed based on the training menu corresponding to the specified class A training management unit that, when the clear condition corresponding to the specified class is established, further shifts the class of the subject to the next class higher than the class,
The respiratory level measuring device according to any one of claims 1 to 24, wherein: An input unit for inputting the bioelectrical impedance of the part including the right lung of the subject measured by the bioelectrical impedance measuring apparatus and the bioelectrical impedance of the part including the left lung of the subject;
Based on the measurement value of the bioelectrical impedance of the part including the right lung, while obtaining the right lung respiration level indicating the ventilation ability of the right lung, while based on the measurement value of the bioelectrical impedance of the part including the left lung, A respiratory level calculation unit for obtaining a left lung respiratory level indicating the ventilation capacity of the left lung,
A respiratory level measuring device characterized by that. A bioelectrical impedance measuring unit that measures bioelectrical impedance for a part including the right lung of the subject and a part including the left lung;
Based on the measurement value of the bioelectrical impedance of the part including the right lung, while obtaining the right lung respiration level indicating the ventilation ability of the right lung, while based on the measurement value of the bioelectrical impedance of the part including the left lung, A respiratory level calculation unit for obtaining a left lung respiratory level indicating the ventilation capacity of the left lung,
A respiratory level measurement system characterized by that.

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